Electrosurgical generator

ABSTRACT

This invention relates to high-frequency ablation of tissue in the body using a cooled high-frequency electrode connected to a high frequency generator including a computer graphic control system and an automatic controller for control the signal output from the generator, and adapted to display on a real time graphic display a measured parameter related to the ablation process and visually monitor the variation of the parameter of the signal output that is controlled by the controller during the ablation process. In one example, one or more measured parameters are displayed simultaneously to visually interpret the relation of their variation and values. In one example, the displayed one or more parameters can be taken from the list of measured voltage, current, power, impedance, electrode temperature, and tissue temperature related to the ablation process. The graphic display gives the clinician an instantaneous and intuitive feeling for the dynamics and stability of the ablation process for safety and control. This invention relates to monitoring and controlling multiple ground pads to optimally carry return currents during high-frequency tissue ablation, and to prevent of ground-pad skin burns. This invention relates to the use of ultrasound imaging intraoperatively during a tissue ablation procedure. This invention relates to the use of nerve stimulation and blocking during a tissue ablation procedure.

This application claims priority to U.S. Provisional Application No.61/989,479, filed May 6, 2014, which is incorporated by reference in itsentirety.

TECHNICAL FIELD

This invention relates generally to the advances in medical systems andprocedures for prolonging and improving human life. The presentinvention relates generally to a system and method for applying energy,particularly radiofrequency (RF) or microwave (MW) energy, to a livingbody. The present invention also relates generally to a system andmethod for apply energy for the purpose of tissue ablation.

BACKGROUND

The use of radiofrequency (RF) and microwave (MW) generators connectedto non-cooled electrodes inserted into the tissue of the body so thatthe signal output from the high frequency (HF) generator ablates thetissue has been used for decades. Both RF and MW generators areconsidered HF generators here. Use of cooled RF and MW electrode systemshave also been in use for decades. Computer graphic systems have beendescribed in use with high frequency ablation systems. The Cosman G4Radiofrequency generator (Cosman Medical, Inc., Burlington, Mass.) is anexample of a modern RF lesion generator that includes a graphic display,and the Cosman G4 brochure printed in 2011 is hereby incorporated byreference herein in its entirety.

A research paper by E. R. Cosman, et al., entitled “Theoretical Aspectsof Radio Frequency Lesions in the Dorsal Root Entry Zone,” Neurosurgery,Vol. 15, No. 6, pp. 945-0950 (1984), describes various techniquesassociated with radio frequency lesions and is hereby incorporated byreference herein in its entirety. Also, research papers by S. N.Goldberg, et al., entitled “Tissue Ablation with Radiofrequency: Effectof Probe Size, Gauge, Duration, and Temperature on Lesion Volume,” Acad.Radiol., Vol. 2, pp. 399-404 (1995), and “Thermal Ablation Therapy forFocal Malignancy,” AJR, Vol. 174, pp. 323-331 (1999), describedtechniques and considerations relating to tissue ablation with radiofrequency energy and are hereby incorporated by reference herein in itsentirety. Examples of high-frequency (HF) generators and electrodes aregiven in the papers of entitled “Theoretical Aspects of RadiofrequencyLesions and the Dorsal Root Entry Zone,” by Cosman, E. R., et al.,Neurosurg 15:945-950, 1984; and “Methods of Making Nervous SystemLesions,” by Cosman, E. R. and Cosman, B. J. in Wilkins R. H.,Rengachary S. S. (eds): Neurosurgery, New York, McGraw-Hill, Vol. III,pp. 2490-2498, 1984, and are hereby incorporated by reference herein intheir entirety. A paper by D. A. Gervais, et al., entitled“Radiofrequency Ablation of Renal Cell Carcinoma: early ClinicalExperience,” Radiology, Vol. 217, No. 2, pp. 665-672 (2000), describesusing a rigid tissue perforating and penetrating electrode that has asharpened tip to self-penetrate the skin and tissue of the patient forthe ablation of kidney tumors, and this paper is hereby incorporated byreference herein in its entirety.

United States patents by E. R. Cosman and W. J. Rittman, III, entitled“Cool-Tip Electrode Thermal Surgery System,” U.S. Pat. No. 6,506,189 B1,date of patent Jan. 14, 2003; “Cluster Ablation Electrode System,” U.S.Pat. No. 6,530,922 B1, date of patent Mar. 11, 2003; and “Cool-TipRadiofrequency Thermosurgery Electrode System For Tumor Ablation”, U.S.Pat. No. 6,575,969 B1, date of patent Jun. 10, 2003 describe systems andmethods related to tissue ablation with radiofrequency energy,generators, and internally-cooled RF electrodes, and they are herebyincorporated by reference herein in their entirety. One electrode systemdescribed in these patents comprises an electrode with an insulatedshaft except for a fixed uninsulated tip exposure of an uninsulatedexposed length, the electrode being internally cooled so that theuninsulated exposed tip is cooled. The electrode shaft is a rigid andself tissue piercing with a sharp pointed distal tip on the electrodeshaft. This is essentially the configuration of cooled electrode offeredby the Radionics Cool-Tip Electrode System (Radionics, Inc., BurlingtonMass.) and the Valley Lab Cool-Tip Electrode System (Valley lab, Inc.,Boulder Colo.). One cooled-RF electrode shown in patent '189 includes anextension tip including a temperature sensor at its distal end. In apatent by Mark Leung, et al., entitled “Electrosurgical Tissue TreatmentMethod”, U.S. Pat. No. 7,294,127 B2, date of patent: Nov. 13, 2007, acooled RF electrode is shown. These patents are hereby incorporated byreference herein in its entirety. The cooled RF system manufactured byBaylis Medical Company (Canada) includes an RF generator maintains thetemperature of an internally-cooled RF electrode substantially below thetissue boiling point, wherein the electrode includes a temperaturesensor positioned in an extension tip at the distal end of the electrodeshaft.

United States patent applications by E. R. Cosman Jr and E. R. CosmanSr. “Cool RF Electrode” application Ser. No. 13/153,696, “Cool RFElectrode” application Ser. No. 14/072,588, and “Cool RF Electrode”application Ser. No. 14/076,113, describe systems and methods related totissue ablation with radiofrequency energy, generators,internally-cooled RF electrodes, and RF cannulae, and they are herebyincorporated by reference herein in their entirety.

The following patents describe microwave tissue ablation devices and areherein incorporated by reference in their entireties: U.S. Pat. Nos.4,641,649, 5,246,438, 5,405,346, 5,314,466, 5,800,494, 5,957,969,6,471,696, 6,878,147, and 6,962,586. Microwave energy is typicallydelivered to tissue by application of a high frequency electromagneticsignal to an elongated antenna probe placed in bodily tissue, withoutthe use of a reference ground pad, wherein the frequency is in the range800 MHz to 6 GHz, for example. Currently the frequencies that areapproved by the U.S. Food and Drug Administration for clinical work are915 MHz and 2.45 GHz. Examples of companies with MW ablation systemsincludes Evident, Covidien, Mansfield, Mass.; MicrothermX, BSD Medical,Salt Lake City, Utah; Avecure, Medwaves, San Diego, Calif.; Certus 140,Neuwave, Madison, Wis.; Amica, Hospital Service, Rome, Italy; andAcculis MTA, Microsulis, Hampshire, England.

Examples of non-cooled electrode systems are in the product lines of thecompanies Cosman Medical, NeuroTherm, Radionics, ValleyLab, Baylis,Kimberly Clark, Stryker, and Diros Medical. Examples of non-cooledelectrode systems with computer graphic display are given in the productlines of Cosman Medical, NeuroTherm, Stryker, Baylis, Kimberly Clark,and Diros. Examples of cooled high-frequency electrode system are shownin the product lines of Covidian, HS Medical, Boston Scientific, andKimberly Clark. Generator systems for RF nerve ablation are included inthe product lines of Cosman Medical, NeuroTherm, Radionics, ValleyLab,Baylis, Kimberly Clark, Stryker, and Diros Medical, and they producemaximum power 50 Watts, attach to up to four electrodes, and attach toone ground pad. Generator systems for RF tumor ablation are included inthe product lines of Covidian, HS Medical, and Boston Scientific, andthey produce maximum power 200 or 250 Watts, attach to up to threeelectrodes, and attach to up to four ground pads. One limitation ofthese RF generators is that they do not provide real-time graphicdisplay of impedance as function of time. One limitation of these RFgenerators is that they do not provide real-time graphic display ofcurrent as function of time. One limitation of these RF generators isthat they do not provide real-time graphic display of both current andimpedance as function of time. One limitation of these generators isthat they do not provide real-time graphic display of both impedance andthe generator output level as function of time. One limitation of thesegenerators is that they do not provide real-time graphic display ofimpedance, current, and temperature as function of time. One limitationof these generators is that they do not provide real-time graphicdisplay any two of the following list: current, voltage, power,impedance, or mathematical functions with these parameters as arguments.One limitation of these RF generators that are configured for cooled RFtissue ablation by means of an automated impedance-driven pulsingprocess is that they do not provide a graphic display of any measuredparameter as a function of time axis. While some generator systems inthe prior art have allowed for export of generator readings which couldbe used to plot parameters on the same time axis after the ablationprocedure, this does not provide instant feedback that would allow aclinician to monitor the ablation process as it progresses and to makeadjustments if necessary. This advantage of real-time graphical doctorfeedback has special importance for cooled-RF tissue ablation, because asingle RF electrode can deliver very high current and heating power toinfluence tissue several centimeters away from that RF electrode (incontrast to typical non-cooled monopolar and bipolar surgicalcoagulation, for example), and because the amplitude and timing ofimpedance and output-level signals can indicate irregularities that canarise from heating over a large volume of tissue that may includemultiple tissue types within different electrical and thermalcharacteristics.

U.S. Pat. No. 5,233,515 A, date of patent Aug. 3, 1993, entitled“Real-time graphic display of heat lesioning parameters in a clinicallesion generator system”, by E. R. Cosman and W. J. Rittman, 111,describes a system for non-cooled RF ablation wherein temperature andimpedance are plotted on the same time axis, and is hereby incorporatedby reference herein in its entirety. One limitation of '515 is that noparameter of the RF generator signal output level (eg voltage, current,power) is plotted as a function of a time. Another limitation of '515 isthat the RF generator signal output level (eg voltage, current, power)is not plotted on the same time axis as the impedance. Anotherlimitation of '515 is that the system does not pertain to RF ablationusing an internally-cooled RF electrode. Another limitation of '515 isthat it does not pertain to automated methods of repeatedly pulsing theRF signal output.

U.S. Pat. No. 6,241,725, date of patent Jun. 5, 2001, entitled “Highfrequency thermal ablation of cancerous tumors and functional targetswith image data assistance”, by E. R. Cosman, describes a system forplanning non-cooled RF ablation using temperature monitoring andcontrol, including plots of various RF parameters. One limitation of'725 is that the system does not pertain to RF ablation using aninternally-cooled RF electrode. Another limitation of '725 is that itdoes not pertain to automated methods for impedance-feedback control ofa cooled RF electrode. Another limitation of '725 is that it does notpertain to automated methods comprising repeated pulsing the RF signaloutput.

Control methods for cooled RF electrodes exist in the prior art whereinthe generator signal alternates between a high range and a low range inresponse to impedance spikes indicative of tissue boiling, whichproduces high-impedance gaseous vapor bubbles around the electrodeactive tip. The paper entitled “Percutaneous radiofrequency tissueablation: optimization of pulsed-RF technique to increase coagulationnecrosis” by S. N. Goldberg et al. (J Vasc Interv Radiol 1999;10(7):907-916) and the paper entitled “High-Power Generator forRadiofrequency Ablation: Larger Electrodes and Pulsing Algorithms inBovine ex Vivo and Porcine in Vivo Settings” by S. A. Solazzo et al.(Radiology 2007; 242(3):743-750) are hereby incorporated by reference infull and describe pulsing processes wherein the RF signal is deliveredat a high, constant-current level until impedance rises above athreshold indicative of boiling (the “up time”); then the RF signallevel is substantially reduced for a predetermined duration (the “downtime”); then the RF output level is returned either to the previous highconstant-current level or to a constant-current level 100 mA below theprevious high constant-current level depending on whether the durationof the previous “up time” was above or below a threshold, respectively;and then the cycle of up times and down times repeats throughout theablation process. Therefore, after an initial rapid ramp (in Solazzo,the initial predetermined current level is achieved in at most 30seconds, at a rate of 67 mA/sec or 134 mA/sec) to bring the RF output toits initial set level, the level of successive constant-amplitude RFpulses monotonically decreases during the ablation process. Onechallenge in cooled RF control by means of impedance-based pulsingmethods is the selection of a target radiofrequency signal level, egcurrent, that can produce a stable ablation process, because the maximumsignal level that particular tissue can carry without overheating andlimiting ablation size, can vary across tissue types, patients, andbodily locations. One limitation of the prior art in impedance-basedpulsing methods for cooled RF ablation control is that the initialoutput level ramp is too fast to discriminate the maximum output levelramp that the tissue can stably carry during the ablation process. Onelimitation of the prior art in impedance-based pulsing methods forcooled RF ablation control is that the output level, namely the currentlevel, does not increase from the initial set value during the ablationprocess. One limitation of the prior art in impedance-based RF pulsingmethods is that if the output level is set low to avoid the risk ofoverheating the tissue, then the maximum ablation size may not achieved,or the maximum lesion size may be not achieved as efficiently aspossible. In one aspect, the present invention seeks to overcome theselimitations by means of an RF pulsing method that can both increase anddecrease the generator output level during up times, eg current, inresponse to measured ablation parameters. Another limitation of theprior art in pulsing methods for cooled RF ablation is that the “downtimes” (that is, the inter-pulse cooling times) do not vary during anablation session. The down times do not vary either in accordance with apredetermined schedule or in response to a measured parameter. This isan important limitation because the extent of the region of boilingtissue bubbles can change during the ablation process, and/or becausethe heat distribution around the bubble zone changes the rate ofdissipation of the bubbles, and/or because a predetermined down-timeduration may not be well matched to the every ablation scenario, leadingto a situation where more or less inter-pulse cooling time is requiredfor optimal dissipation of vapor bubbles in the tissue. In one aspect,the present invention seeks to overcome these limitations by means of anRF pulsing method wherein the down-time durations (ie the cooling timein between pulses) can vary during the ablation process. In someembodiments of the present invention, the variation of down times caninclude a component that is predetermined, as in the example of apredetermined schedule of increase in the down-times durations. In someembodiments of the present invention, the variation of down times caninclude a component that is influenced by one or more measuredparameters during the ablation process. In various embodiments of thepresent invention, the variation of down times can either strictlyincrease, strictly decrease, or both increase and decrease. Anotherlimitation of prior systems for RF tissue ablation is that they do notplot both the impedance and the generator output level (eg voltage,current, or power) on the same time axis in real time. Anotherlimitation in the prior art is that prior systems for RF tissue ablationdo not include a plot of two or more of the parameters impedance,voltage, current, and power. Another limitation in the prior art is thatprior systems for RF tissue ablation do not include both an automaticmethod for output-level pulsing (eg for cooled RF tissue ablation) and areal-time graphical plot of a parameter of the generator output (egvoltage, current or power, impedance) as a function of time. Severalaspects of the present invention seek to overcome these limitations.

In U.S. Pat. Nos. 8,152,801 and 8,357,151 by Goldberg and Young, an RFpulsing method for non-cooled RF ablation is proposed wherein the levelof successive constant-amplitude RF pulses monotonically decreasesduring the ablation process in response to impedance variationsindicative of tissue moisture content.

The use of radiofrequency (RF) generators and electrodes to be appliedto tissue for pain relief or functional modification is well known.Related information is given in the paper by Cosman E R and Cosman B J,“Methods of Making Nervous System Lesions”, in Wilkins R H, Rengachary S(eds.); Neurosurgery, New York, McGraw Hill, Vol. 3, 2490-2498; and ishereby incorporated by reference in its entirety. Related information isgiven in the book chapter by Cosman E R Sr and Cosman E R Jr. entitled“Radiofrequency Lesions.”, in Andres M. Lozano, Philip L. Gildenberg,and Ronald R. Tasker, eds., Textbook of Stereotactic and FunctionalNeurosurgery (2nd Edition), 2009, and is hereby incorporated byreference in its entirety. For example, the RFG-3C plus RF lesiongenerator of Radionics, Inc., Burlington, Mass. and its associatedelectrodes enable electrode placement of the electrode near targettissue and heating of the target tissue by RF power dissipation of theRF signal output in the target tissue. For example, the G4 generator ofCosman Medical, Inc., Burlington, Mass. and its associated electrodessuch as the Cosman CSK, and cannula such as the Cosman CC and RFKcannula, enable electrode placement of the electrode near target tissueand heating of the target tissue by RF power dissipation of the RFsignal output in the target tissue. Temperature monitoring of the targettissue by a temperature sensor in the electrode can control the process.Heat lesions with target tissue temperatures of 60 to 95 degrees Celsiusare common. Tissue dies by heating above about 45 degrees Celsius, sothis process produces the RF heat lesion. For pain management, RFgenerator output is also applied to nerves using a type of pulsed RFmethod, whereby RF output is applied to tissue intermittently such thattissue is exposed to high electrical fields and average tissuetemperatures are lower, for example 42 degrees Celsius or less; this isdifferent from the RF pulsing methods for tissue ablation, such as thatdescribed in Goldberg et al. (1999) and in embodiments of the presentinvention, wherein the clinical objective is to heat large volumes oftissue surrounding the active tip to destructive temperatures, includingtemperatures that induce tissue boiling. High temperatures in painmanagement pulsed RF are undesired and are only sometimes present oververy small regions (eg less than 0.33 mm in radius) near point of highcurvature on active electrode tip, as described in an article by E. R.Cosman Jr. and E. R. Cosman Sr. entitled “Electric and thermal fieldeffects in tissue around radiofrequency electrodes” (Pain Medicine 2005;6(6): 405-424) which is hereby incorporated by reference in full. Thisis different the temperature profile produced by RF tissue ablationwherein approximately ellipsoidal high-temperature isotherms surroundthe electrode active tip and spread several millimeters or severalcentimeters from the active tip, thereby heating a substantially portionof the tissue in contact with the electrode active tip to a destructivetemperature. The pain-management pulsed RF method is applied with pulsesof RF that have duration in the range less than 50 milliseconds, withthe RF level at zero in between pulses, and with pulse repetition ratesof 1 to 10 Hz, so that the duration of each period wherein the RF is onis less than 50 milliseconds, and the duration of each period whereinthe RF is off is less than 1000 milliseconds; this is different from RFpulsing methods for control of tissue ablation electrodes, such as thatdescribed for cooled RF in Goldberg et al. (1999) and in embodiments ofthe present invention, wherein the duration of each period in which RFis applied at a high level configured to substantially heat the tissuetypically greater than 10 seconds and can be as long as the total timeof the ablation process, and wherein the duration of each period whereinthe RF is applied at a low level configured to allow tissue cooling istypically between 5 and 50 seconds. The pain-management pulsed RF methodeither adjusts the signal parameters pulse amplitude, pulse rate, andpulse width in response to a measured temperature; or fixes thesevalues; and does not terminate and initiate RF pulses in response toeither indications of tissue boiling, indications of tissue cooling, theexpected duration of tissue cooling between RF pulses, or the value orvariations of a measured impedance, current, voltage, or power. This isdifferent from RF pulsing methods for control of tissue ablation, suchas that described for cooled RF in embodiments of the present inventionand in Goldberg et al. (1999), wherein the up times are terminated by arise in impedance, and the down times have a duration configured toallow for the dissipation of high-temperature and high-impedance gasformed around the active electrode tip. The RF pulses in thepain-management method of pulsed RF are configured to reduce tissueheating; whereas the RF pulses in tissue-ablation pulsed RF methods,such as those presented in the present invention, are configured tomaximize tissue heating. The durations of low signal level between RFpulses in the pain-management method of pulsed RF are not configured toallow for dissipation of gas bubbles distributed around the electrodeactive tip; whereas the durations of low signal level between RF pulsesin the pulsed-RF methods of the present invention are configured toallow for dissipation of large gas bubbles distributed around theelectrode active tip. The level of RF pulses in pain-management pulsedRF are not configured to increase a heat lesion size; whereas the levelof RF delivered during the on periods of embodiments of the presentinvention are configured to increase the size of a heat ablation volume.

A significant difference between non-cooled electrode systems and cooledelectrode systems is in the means of controlling the ablation process.For non-cooled electrode systems, the maximum tissue temperature issubstantially at or near the surface of the electrode, so measuring theelectrode temperature by a temperature sensor in the electrode, one candirectly control the ablation process. For a given electrodetemperature, size of electrode, and time of heating, you can predictreliably ablation size as described in the papers entitled “TheoreticalAspects of Radiofrequency Lesions and the Dorsal Root Entry Zone,” byCosman, E. R., et al., Neurosurg 15:945-950, 1984, and “BipolarRadiofrequency Lesion Geometry: Implications for Palisade Treatment ofSacroiliac Joint Pain.” By E. R. Cosman Jr and C. D. Gonzalez, PainPractice 2011; 11(1): 3-22, which are herein incorporated by referencein their entireties. For non-cooled electrodes it is also possible toprevent the instability point of boiling of tissue, explosive gasformation, and charring of tissue by direct control of the HF generatorsignal output so the electrode temperature does not exceed 100° C. asdescribed a monograph entitled “Guide to Radio Frequency LesionGeneration in Neurosurgery” by B. J. Cosman and E. R. Cosman, Radionics,Burlington, Mass., 1974.

A cooled-electrode HF ablation system differs from anon-cooled-electrode HF ablation system in that the maximum tissuetemperature is at a distance from the electrode. The maximum tissuetemperature around a cooled electrode occurs in a zone around theelectrode tip, but at a distance from the electrode tip. The electrodeis cooled so the electrode temperature is not typically a direct measureof the maximum tissue temperature, unlike non-cooled electrode systemswherein the maximum tissue temperature can be measured almost directlyby means of the non-cooled-electrode's temperature sensor.Cooled-electrode HF ablation using an satellite temperature sensor, suchas an extension tip containing a temperature sensor, can betemperature-controlled to prevent tissue boiling; this is different fromcooled-electrode HF ablation in which the tissue temperature is notmonitored (such as the case wherein the electrode does not contain atemperature sensor, or the case wherein the electrode temperature sensoris within the flow of coolant within the electrode) and the electrode isallowed to raise tissue temperatures into the boiling range.

The use of RF energy in neural tissue for the treatment of pain andfunctional disorders is well known. A typical nerve ablation protocolincludes a first step in which one or more nerve stimulation signal isapplied to an RF electrode for guidance of that electrode, and the asecond step in which RF energy is applied to the RF electrode to ablatetissue near the electrode active tip. Typical nerve stimulation signalsinclude biphasic electrical pulses delivered at a rate of up to 200 Hz,typically 50 Hz for sensory nerve stimulation and 2 Hz for motor nervestimulation. Another well-known clinical use of high-frequency energy isthe ablation of large tumors; this requires putting large amounts ofpower from the electrode into the tissue. This will cause the zone ofmaximum temperature to exceed 100 degrees C. That will cause the tissueto boil and bubbles to form in the zone of maximum temperature. This canbe a rapidly explosive process and an unstable process. For tumorablation performed using a cooled electrode, the temperature measuredinside the cooled electrode is not a direct indication of the zone ofinstability. However, the instability is reflected in other signaloutput parameters, including, for example, the signal output impedance,power, current, and voltage. The above background references do notteach how to control the cooled HF electrode process when the generatorsignal output is increased so that the process is pushed into the regionon of instability, nor do they show or teach how to maintain and monitoran ablation process that is held close to the instability point for theduration of the process.

U.S. Pat. No. 7,736,357 by Lee et al. (hereinafter “Lee”) presents aradiofrequency ablation system wherein RF current from an ablationelectrode is switched between two or more ground pads in a repeatingsequence wherein only one ground pad is active at a time. One limitationof the prior art in Lee is that it does not provide for simultaneousactivation of multiple ground pads at the same time during a switchingsequence. Another limitation of Lee is that the peak current at eachground pad is identical and equal to the total current delivered to oneor more ablation electrodes. This peak current can be very high, and canlimit the total current that can be delivered by the ablationelectrodes. Another limitation of the prior art in Lee is that thesequence of switch states is predetermined, alternating sequentiallyamong a number of ground pads. Another limitation of the prior art inLee is that the sequence of switch states is not based on a measurementof a ground pad parameter. Another limitation of the prior art in Lee isthat a sequential ground-pad switching sequence does not generallyminimize tissue heating for each ground pad relative to other switchingsequences. Another limitation of the prior art in Lee is that asequential ground-pad switching sequence does not maximize the totalablation current that a configuration of ground pads can carry, acrossall possible ground-pad switching sequences. Another limitation of theprior art in Lee is that it does not provide a switching method that cancontrol both the total rate of heating in tissue adjacent to two or moreground pads, and the rate of heating in the tissue region adjacent toeach one of the said two or more ground pads. In the prior art in Lee,for a given total current I delivered N ground pads by the ablationelectrodes, the total average heating power delivered to tissue incontact with the two or more ground pads is proportional to (I²*t₁/t)+ .. . +(I²*t_(N)/t)=I², where t_(i) is the duration of i-th phase of theswitching sequence in which only the i-th pad is connected and carryingcurrent, and where t=t₁+ . . . +t_(N) is the total duration of one cycleof the switching sequence. Therefore, while the average heating powerdelivered to the i-th pad (which is proportional to the RMS currentI²*t₁/t delivered to the pad over the cycle period) can be controlled byadjustment of the duration t_(i), the total average heating power isinvariant variations in the timing of the switching pattern. Anotherlimitation of Lee is that a cyclic switching sequence does not maximizethe total current which can be carried by a set of ground pads, wherethe RMS current each ground pad is held below a safety limit. Anotherlimitation is that the system of Lee does not reduce the number ofswitching transitions. Another limitation is that the system of Lee doesnot provide for both switching and independent current-monitoring foreach pad.

The papers “Sequential Activation of a Segmented Ground Pad Reduces SkinHeating During Radiofrequency Tumor Ablation: Optimization viaComputational Models”, IEEE Trans Biomed Eng. 2008 July; 55(7): 1881-9by D. J. Schutt and D. Haemmerich; “Sequential activation of ground padsreduces skin heating during radiofrequency ablation: Initial in vivoporcine results” Conf Proc IEEE Eng Med Biol Soc. 2009; 1:4287-4290 byD. J. Schutt et al.; and “Sequential Activation of Ground Pads ReducesSkin Heating During Radiofrequency Tumor Ablation: In Vivo PorcineResults” IEEE Trans Biomed Eng 2010 March; 57(3):746-753 by D. J. Schuttet al. describe switching of power-regulated RF output to three groundpads in known positions relative to each other, wherein each padincludes a temperature sensor, wherein the switching sequence maintainsthe temperatures at a set level, and wherein the switching producesrepeated cycles of the sequence: (1) proximal, middle, and distal groundpads activated; (2) middle and distal ground pads activated; and (3)only distal ground pad activated. One limitation the papers of Schutt etal. is that they do not provide for control the current carried by anyone of the ground pads in relative to a target current value or amaximum current value. One limitation the papers of Schutt et al. isthat they do not provide for automatic control of the root-mean-squared(RMS) current at each pad over each switching cycle. Another limitationof the papers by Schutt et al. is that integration of temperaturesensors into the ground pads is required. One limitation preventingground pad burns by temperature monitoring is that the temperaturesensor may not directly or reliably measure the temperature of heatedtissue, for example, in the case where the ground pad is not fullyadhered to the skin. Another limitation of the papers by Schutt et al.is that the relative position of the ground pad was known ahead of timeand used to set up the switching process manually, rather thanautomatically by means of a controller based on a measured parameter ofa ground pad. Another limitation of the papers by Schutt et al., is thatneither the ground-pad switch states (as reflected by the identities ofthe connected ground pads and disconnected ground pads) in the sequence,nor the order of the switch states in the sequence, was determined by anautomatic controller using a measured ground-pad parameter. Anotherlimitation of the papers by Schutt et al., is that the identity andorder of switch states is predetermined. Another limitation of thepapers by Schutt et al. is that they do not provide for both switchingand current monitoring at each pad individually. Another limitation ofthe papers by Schutt et al. is that ground pad switch was used inconjunction with an ablation electrode output that was set to a constantpower, which can lead to variable current density around the electrodeactive tip as ground pads are connected and disconnected, and thuspotentially leading to inconsistent lesion sizes at the ablation site.Another limitation of the papers by Schutt et al. is that they do notprovide for both switching and independent current-monitoring for eachpad.

U.S. Pat. No. 7,566,332 by Jarrard and Behl presents a radiofrequencyablation system wherein the RF current flowing to each of two or moreground pads from an ablation electrode is balanced by adjusting alimited amount added resistance between the ground pad and the RF powersupply. One limitation of adding resistance between a ground pad and thepower supply is that generated electrical energy is dissipated in theresistance and does not heat the target tissue, thereby limiting themaximum heating power that the generator can produce. One limitation ofthe prior art in '322 is that the variety of ground pad configurationsto which the system can adapt is limited by the limited amount ofresistance that is added to each ground pad line during an ablationprocedure.

Another limitation of the prior art is that RF ablation systemsconfigured for nerve ablation do not include means for connection andmonitoring of multiple ground pads. This is a significant limitation forenergizing multiple nerve ablation electrodes in a single patient at thesame time, which can produce high currents in excess of current capacityof a single typical nerve-ablation ground pad.

Another limitation of the prior art on ground pad switching in Lee andSchutt et al. is that they do not provide for the prevention orreduction of electrical stimulation of excitable tissue that can occurdue to transient direct-current signals that can arise when a switchopens or closes. Undesired stimulation of excitable tissue can occur ata site remote of the ground pads and ablation electrodes. Undesiredstimulation of nerves can occur, and be disturbing to the patient, dueto high electric field strengths near the active tip of an RF ablationelectrode and transients produced by connection or disconnecting aground pad from the source of the RF ablation signal.

U.S. Pat. Nos. 6,575,969 and 6,506,189 by Rittman and Cosman, and U.S.Pat. No. 6,241,725 by E. R. Cosman relate to the use of ultrasoundimaging data for tissue ablation. In the prior art, ultrasound imagingapparatuses are physically separate from HF ablation generators, andthere is no connection between an ultrasound imaging device and a HFablation generator for unified control of both devices, image andparameter display, and procedure documentation. One limitation the priorart in ultrasound image guidance for tissue ablation is that thephysician must use a two sets of controls to operate both the ultrasoundimaging device and the HF ablation generator. In one example, theabsence of a single user interface for control and monitoring of bothultrasound imaging and ablation readings is a limitation forultrasound-guided cooled RF tumor ablation using an RF pulsing processthat repeatedly induces tissue boiling, because the ultrasound imagesand the RF generator readings both provide rich information to theoperating physician who, as does the correlation of ultrasound featuresand features of RF generator readings (eg echogenic bubble formation andvariations in RF impedance. Another limitation of the prior art is theabsence of automated influence of the ablation process using ultrasoundimaging data as an input.

The use of RF energy in neural tissue for the treatment of pain andfunctional disorders is well known. A typical nerve ablation protocolincludes a first step in which one or more nerve-stimulation signalconfigured to induce repeated nerve firing, is applied to an RFelectrode for guidance of that electrode to a target position near anear, a second step in which a fluid anesthetic is injected to preventperception of pain during the nerve ablation, and a third step in whichRF energy is applied to the RF electrode to ablate tissue near theelectrode active tip. Typical nerve stimulation signals include biphasicelectrical pulses delivered at a rate of up to 200 Hz, typically 50 Hzfor sensory nerve stimulation, and typically 2 Hz for motor nervestimulation. One limitation of the prior art is that RF andnerve-stimulation signals are not applied at the same time to a singleperipheral nerve. One limitation of the prior art is that RF andnerve-stimulation signals are not applied at the same time to a singleperipheral nerve, and firing in that nerve is not monitored at the sametime. One limitation of the prior art is that RF and nerve-stimulationsignals are not repeatedly interleaved to provide for nerve stimulationthroughout an RF ablation process. One limitation of the prior art isthe response of a nerve to a stimulation single is not used as astopping criteria for an RF nerve ablation. Another limitation of theprior art is that an RF generator configured for nerve ablation does notproduce nerve stimulation signals that are configured to electricallyblock the transmission of action potentials within a nerve, such as ahigh-frequency block signal.

The present invention overcomes the stated disadvantages and otherlimitations of the prior art.

SUMMARY OF THE INVENTION

The following are examples of embodiments of the systems and methods ofthe present invention. Further examples and details are given in theDescription and Claims sections.

Some embodiments of the present invention include a cooled HF electrode,coolant supply, control system for automatic control of the ablationprocess, and computer graphic display.

In one exemplary embodiment, the present invention is directed towardssystems and methods for ablating tissue in the living body. This caninclude using a combination of a radiofrequency generator, a graphicaldisplay of impedance and generator output level, a controller includingan automatic master controller for modulating the radiofrequencygenerator output level in response to changes in tissue impedance, acoolant pump, multiple ground pads with current monitoring andswitching, a cooled radiofrequency electrode system adapted for creatinglarge ablation volumes, an ultrasound imaging system, and a single userinterface that provides for control of both the radiofrequency generatorand the ultrasound imaging system. In one application, the presentinvention is directed towards thermal tissue ablation, includingablation of cancerous tumors and nerve ablation for pain management.

In one example of the present invention, at least one of generatorsignal output parameters from the list of impedance, power, current, andvoltage is displayed in real time as a function of a displayed timeaxis, and variations in the graph of the parameter reflect variations inthe generator signal output to maintain the system near the unstablebubble zone around the electrode. One advantage of this is that theclinician gets an instant intuitive visual feeling for the stability ofthe ablation process.

In another example of the present invention, two or more parameters fromthe list of impedance, power, current, and voltage are displayedsimultaneously and stacked on the same display and versus the same timescale axis. One advantage of this is the clinician gets an instantvisual feeling for the relative variation of parameters to access if theablation process is going properly according to the automaticcontroller.

In another example of the present invention, generator signal outputimpedance is displayed with one or more of the output parameters fromthe list of power, current, and voltage on the same display and versusthe same displayed time axis. One advantage of this is that an upwardspike in impedance that indicates that the unstable bubble zone isincreasing rapidly is accompanied simultaneously with displayed signaloutput, which should be moderated, either by the user or an automaticcontroller, to stop the unstable explosive bubble formation according tothe controller programming. This joint display of impedance and outputlevel can be of particular importance in controlling a cooled RFelectrode by feedback on measured impedance (for example, in the casewhere the electrode does not measure temperature, or the measuredtemperature is not representative of the tissue temperature as in thecase where the temperature sensor is positioned within the coolant flowwithin the electrode) when the tissue is repeatedly heated to the pointof boiling by the electrode, so the physician can assess, makepredictions about, troubleshoot, and make adjustments to an ablationprocess that can involve multiple phases with variable featuresdepending on electrode geometry and tissue condition. This joint displayof impedance and output level can be of particular importance in amethod of impedance-based pulsed RF control of cooled RF electrodewherein the pulse signal amplitude can both increase and decrease duringthe ablation process. This joint display of impedance and output levelcan be of particular importance in a method of impedance-based pulsed RFcontrol of cooled RF electrode wherein the inter-pulse period can changein duration during the ablation process. This joint display of impedanceand output level can be of particular importance in a method ofimpedance-based pulsed RF control of cooled RF electrode wherein thepulse signal amplitude can both increase and decrease, and theinter-pulse period can change in duration during the ablation process.

In another example of the present invention, the cooled electrode at itsdistal end has extension tip with indwelling temperature sensor tomeasure temperature at a distance from the electrode active tip in theregion of maximum tissue temperature distal to the electrode active tip,and the maximum tissue temperature being displayed simultaneously on thesame display as the measured generator signal output parameters. Oneadvantage of this is that the accessory external temperature measured atthe maximum tissue temperature where the bubble zone forms can be usedto by the control system to control the ablation process. In anotherexample, the cooled electrode has an extension tip that protrudes fromthe side of the electrode active tip, wherein the extension tip includesa temperature sensor that measures a temperature at a lateral distancefrom the main active tip. One advantage of an external temperaturesensor at the side of the active tip is that the progress of the lesionalong the side of the electrode can be monitored and the lateral extentof the heat lesion can be estimated. In some embodiments, the extensiontip is electrically conductive and is a part of the active tip. In someembodiments, the extension tip is not electrically conductive and doesnot deliver electrical signal output to the tissue. In some embodiments,the extension tip is metallic but is not electrically connected to thegenerator signal output, and thereby the temperature sensor in theextension tip has a fast thermal response and is not itself generatingheat in the tissue; in this embodiment, the thermosensor in theextension tip can include thermal insulation between it and the coolantflowing in the electrode (including in one example, an air gap betweenthe thermosensor and the coolant flow); this has the advantage of moreaccurate sensing of tissue temperature at a distance from the electrodeactive tip.

For a cooled electrode system, the prediction of ablation size is lessdirect than for non-cooled systems because of its intrinsic instabilityat maximum signal output and the dependence on non-thermal measuredparameters, including signal output power, current, voltage, andimpedance. The prior references do not show or teach how to predict, norhow to allow the physician to predict, cooled-electrode ablation size inthe case that the process is maintained near the instability regiondescribed above.

Another significant factor is monitoring the relation of variation oftwo or more of the signal output parameters including impedance,current, power, and voltage, as well as an external temperature readingif that is available. This is optimally done on a visual display withthe graphs of each displayed parameter registered on the same timescale. None of the cited prior references shows or teaches about thisaspect of the ablation control and monitoring.

Another objective of this patent is to display the graph of two or moreof the parameters from the list of signal output impedance, power,current, and voltage, as well as an external temperature reading ifavailable, on a computer graphic display, the graphs being stacked orsuperimposed and registered to the same time scale shown on the computergraphic display.

In another aspect, it is important that the clinician has a real timeand intuitively clear visual interpretation of the ablation process fromits beginning and how the control system and stability of the process isworking. The clinician should be able to discriminate different graphson the computer graphic display in the dim light of an operating roomand from a distance, for example by means of color-coding of graphs ofdifferent parameters. None of the prior references show or teach thesecriteria.

Another objective of the present invention is to provide clearly visibleand intuitively obvious real-time and historically-complete computergraphic display of the ablation parameters related to the control of theprocess.

One objective of the present invention is to describe a system tocontrol and monitor the cooled electrode ablation process using apulsing control method and computer graphic display of one or more ofthe signal output parameters power, current, and voltage. Anotherobjective of the present invention is to describe a system and methodfor prediction of ablation size using a pulse control process executedby the control system, and using computer graphic display of signaloutput parameters to monitor the stability of the ablation process.

In one example, the control method is adapted to ramp up the signaloutput power, current, or voltage according to the control method to adesired level, and then turn off and on the signal output triggered byupward impedance spikes and determined by desired durations of on andoff times as well as desired output levels during the on times tomaintain a steady state of the ablation process near the bubbleinstability to maximize ablation size, wherein all of this informationis displayed in real time in the graphic displays of impedance, currentand/or power. One advantage of this is that it gives an instantintuitive and visual feeling to the clinician about the course of theablation process and whether it is working in a desired manner. Oneadvantage of this is that the lesion size produced by a cooled ablationprobe can be increased by means of automated, impedance-based pulsing ofthe signal output by a controller and display to the physician of visualinformation about the actions taken by the controller.

In one example, the amplitude of the pulses of signal output power isincreased and decreased during the ablation process in response tomeasured parameters. In one example, the inter-pulse period of lowsignal output are increased and decreased during the ablation process inresponse to measured parameters. One advantage of this is that the pulseamplitudes, pulse duration, inter-pulse duration can be adjusted inresponse to the conditions of a particular ablation process.

In some embodiments of the present invention, a radiofrequency generatorsystem includes a first setting for the initial pulse output level, asecond setting for the maximum pulse output level, and a controller thanproduces a series of pulses of radiofrequency signal output, each pulsebeing terminated in response to a measured indication of tissue boiling(such as an impedance rise); the signal output level during the pulsesboth increasing and decreasing during a single automated ablationprocess in accordance with the first setting and the second setting; andthe output level and duration between pulses being set to a low levelconfigured to allow for tissue cooling.

In one example, the patient has one or more ground pads as referenceelectrode for carrying return current from the cooled electrode, and theHF generator being adapted to measure the impedance and/or temperatureof and/or current to the ground pads and one or more of these quantitiesbeing displayed on the computer graphic display in real time and on thesame display as the measured generator signal output parameters. Oneadvantage of this is that the ground pads can be monitored for faultsthat could result in skin burns. Another advantage is the ground padcurrents can be regulated and/or equalized.

In another example, an RF generator system includes connections formultiple electrodes and multiple ground pads, and radiofrequencyablation can be effected at multiple electrodes at the same time; inthis example, the generator provides user controls for activating anddeactivating each electrode, changing the settings for each electrodeindividually or collectively, and selecting the electrical potentialsand patterns of switching electrical potentials to each other electrodesto effect radiofrequency ablation configurations including monopolar,bipolar, dual, multipolar, clustered, and sequences thereof; in someembodiments of this example, the system can include a controller thatdistributes current from the electrodes among the ground pads bysequentially connecting and disconnecting different subsets of theground pads to source of the electrode current.

In another example, a radiofrequency generator switches current from oneor more ablation electrodes among two or more ground pads in a sequencewherein two or ground pads carry current from the ablation electrodes atthe same time at some point in the sequence. In another example, aradiofrequency generator maximizes the amount of time during whichcurrent is distributed among multiple ground pads in a ground padswitching sequence configured to regulate the current carried by eachground pad. In another example, a radiofrequency generator selects asequence of ground pad connections that minimizes the current carried byeach ground pain for a given, general ground pad configuration. Inanother example, a radiofrequency generator automatically executes aprocess that selects a sequence of ground pad switch configurations, andthe timing of that sequence, to reduce the current carried by eachground pad, for an arbitrary configuration of two or more ground padsand one or more ablation electrodes. In another example, aradiofrequency generator executes a process comprising selecting asequence of ground pad switch configurations, and the timing of thatsequence, to regulate ground pad heating based on measurement of aparameter related to ground pad heating. One advantage of this aspect,is that the process can adapt to an arbitrary ground pad setup withoutuser input.

One objective of the present invention is to describe a system toreliably limit the heating of tissue in contact with ground pads used tocarry return currents during ablation processes. Switching HF signaloutput among ground pads placed on the skin surface is different fromswitching HF signal output among ablation electrodes, in part becausethe former is configured to prevent or limit effects such as tissueheating near the ground pads, and the latter is configured to induce aclinical effect such as heat tissue near ablation electrodes. Generally,the skin heating is influenced by ohmic heating within the tissue volumeadjacent to the area of ground pad contact. Ohmic heating is influencedby the local average power density, which is in turn influenced by theRMS current carried by the ground pad. By the principle of currentconservation, the RMS current carried by a ground pad from anotherelectrode can be predictive of ohmic heating power dissipated in tissuein close proximity to the ground pad, irrespective of other power lossesand voltage drops in the conduction path between the ground pad and theelectrode. In one aspect, the present invention is related to themeasurement and control of the RMS ground-pad current over time windowsthat are short relative to the thermal response of tissue in contactwith a ground pad, because this kind of RMS ground-pad current is ameasurable parameter that relates to the rate of heating and thetemperature increases in tissue that is in contact with a ground pad. Inone aspect, the present invention relates to measurement of the currentat each of two or more ground pads to prevent ground-pad skin burnsduring RF ablation procedures. In another aspect, the present inventionrelates to repeatedly connecting and disconnecting each of two or moreground pads during a RF ablation procedure to control the RMS currentcarried by each pad, and thereby to provide for the delivery of higheroutput currents to ablation electrodes while preventing skin burns. Inanother aspect, the present invention relates to avoiding undesiredstimulation of excitable tissue as a result of ground pad switching. Inanother aspect, the present invention relates to maximizing the amountof time that multiple ground pads attached to the system are carryingreturn currents from ablation probes in order to reduce overall skinheating.

In another aspect, the ablation process, when dealing with very largetumors, can require as much as 200 to 400 watts of power into the bodytissues, or more. For a medical RF procedure where return of currentfrom the RF electrode is carried by one or more large area ground padsthat are applied to the skin, a risk is that if the ground pad(s) is/arenot fixed on the skin properly or is defective, then skin burns canoccur. The prior references above do not show or teach solutions to thisproblem wherein an RF ablation system can adapt to an arbitraryarrangement of ground pads on a patient's skin surface.

Another objective of the present patent is to provide control andsafeguards to reduce the chance of skin burns at the ground pads. Inanother aspect, the present invention relates to avoiding ground padskin burns produced by a system for RF nerve ablation that produces highoutput levels, as in the case of multi-electrode RF nerve ablationsystems.

In another example, a radiofrequency generator includes controls bothfor radiofrequency lesioning and for an ultrasound imaging device, sothat ultrasound image-guidance for radiofrequency ablation, and theradiofrequency ablation itself, can be controlled from a single console;in a more specific example, the radiofrequency ablation is performedusing an cooled RF electrode to which output is delivered usingimpedance-controlled RF pulses. In another example, ultrasound imagingdata can be used as an input to a HF ablation controller and can affectthe control of a HF ablation process, such as RF and MW ablation. Forexample, indicators of tissue changes due to ablation, such as changesrelated to tissue temperature or the formation of gas bubbles, can beused to control the ablation process, either by an automatic process, byuser adjustments, or both. For example, as described in a paper entitled“Ultrasound Monitoring of in Vitro Radio Frequency Ablation by EchoDecorrelation of Imaging” by T. Douglas Mast et al. (J. Ultrasound Med2008; 27:1685-1697), ultrasound imaging data can provide estimates oftissue temperature in the liver.

In another example, a radiofrequency generator includes a nervestimulator and multiple ground pad connections. In this example,multiple ground pads can provides for higher total output in nerveablation procedures. This can provides for ablation of multiple nervesusing of multiple electrodes at the same time, nerve ablation using oneor more large electrodes, and nerve ablation using one or more cooledelectrodes, using standard electrosurgical ground pads.

In another example, a radiofrequency ablation system can produce a nervestimulation signal and an RF ablation signal at the same time. This canprovide for monitoring of nerve stimulation response during the ablationprocess. This can provide for a termination criteria for a nerveablation process. This can provide for a means of determining thesuccess of a nerve ablation procedure. This can provide for reduction ofpain during a nerve ablation procedure. This can provide for thereduction of pain during a nerve ablation procedure without the directapplication of anesthetic to the nerve, thereby allowing for evaluationof the efficacy of the nerve ablation soon after the ablation iscomplete.

The present invention can be used in numerous organs in the body,including the brain, spine, liver, lung, bone, kidney, and abdominalstructures; and for the treatment or partial treatment of canceroustumors, other pathological target volumes, or other types of tissuetarget volumes in, for example, nervous tissue, a nerve located within abone, bone tissue, cardiac tissue, muscle tissue, or other types ofbodily tissues.

Other examples of embodiments of the invention are given in the rest ofthis patent. The details of embodiments of the invention are set forthin the accompanying drawings and description below. Other features,objects, and advantages of the invention will be apparent from thedescription and drawings and from the claims.

BRIEF DESCRIPTION OF THE DRAWINGS

In the drawings that constitute a part of the specification, embodimentsexhibited various forms and features hereof are set forth, specifically:

FIG. 1A is a schematic diagram showing a HF electrosurgical systemconfigured for tissue ablation including an internally-cooled ablationprobe comprising an internally-cooled electrode inserted into a RFcannula; one or more ground pads each with a current monitoring circuit;a coolant pump; an ultrasound machine; digital display of a HF outputlevel parameters (voltage, current, and power), impedance, ablationprobe temperature, and elapsed lesion time; a graphical user interfaceincluding graphs of impedance, HF output level, and temperature overtime; a pulsing process that alternates between high and low levels ofHF output and adjusts the high level of HF output in response to spikesin measured impedance; a HF generator in a front elevation view,including jacks for at least one ground pad; jacks for at least onecooled HF ablation probe; a graphic display including user controls,documentation functions, display of the current carried by each groundpad, and a graphs of ablation probe HF output level, impedance, andtemperature plotted on the same time axis in real time; mechanical usercontrols; jacks for peripheral user interface devices; a jack forprinting; a jack for data export; a jack for network connectivity; alink to, and controls for, the ultrasound machine; wherein the graphsreport increments and decrements in the HF ablation probe output inresponse to ablation probe impedance readings, including the drasticreduction of current in response to rapid rises in impedance indicativeof boiling tissue around the ablation probe active tip.

FIG. 1B is a schematic diagram showing a HF electrosurgical system fortissue ablation wherein a cooled HF electrode includes a temperaturesensor on a distal extension tip, and a HF generator measures andregulates the temperature from the temperature sensor; wherein theelectrical current flowing to each of multiple ground pads is measured,displayed to the user, and automatically controlled; wherein a HFgenerator includes an operative connection to an ultrasound machine anduser controls for that ultrasound machine.

FIG. 1C is a schematic diagram showing a system for HF tissue ablationwherein an internally-cooled cluster of electrodes is attached to signaloutput of a HF electrical signal generator; wherein each independentshaft of the clustered electrodes includes an active region fortransmission of HF signal output to the patient and a temperature sensorpositioned within the flow of coolant within the shaft; wherein theelectrodes are constrained in a parallel triangular configuration by aguideblock through which the shaft of the electrodes pass; wherein thegenerator automatically pulses the signal output in response tovariations in the impedance encountered by signal output delivered tothe electrode cluster that indicate boiling and cooling in tissue heatedby the electrode cluster; wherein a graphic display plots on one timeaxis, in real time, the signal output level delivered to the electrodecluster, the impedance encountered by the signal output to the electrodecluster, and each of the temperatures measured by the electrode cluster;wherein multiple ground pads carry return current from the clusterelectrode; wherein the current carried by each ground pad is measured,displayed to the user, and are maintained under a maximum limit; whereinthe HF signal generator includes an operative connection to anultrasound machine and user controls for that ultrasound machine.

FIG. 2 is a schematic diagram showing a HF system for tissue ablationthat includes multiple independent ablation electrodes that areinternally-cooled; a radiofrequency generator that can energize theablation electrodes in a variety of configurations of connection to thegenerator output potentials, including monopolar, bipolar, andmultipolar configurations; graphic plotting of signal output level,impedance, and temperature for each electrode on a time axis in realtime; multiple ground pads that carry return currents from the multipleablation electrodes, wherein the current flowing through each ground padis measured, displayed to the user, and regulated; and user-controlsfor, and an operative connection to, an US machine.

FIG. 3 is a schematic diagram of a real-time graphical display ofparameters of a cooled-RF tissue ablation process that is controlled byan RF pulsing method whereby the RF signal alternates between a highlevel configured to substantially heat the tissue, and a low levelconfigured to allow for cooling of heated tissue; whereby after aninitial high level RF signal is set, the high signal level bothincreases and decreases; and whereby the duration of periods varies inwhich a low level is delivered, based in part on measured parameters ofthe ablation process.

FIG. 4 is a flow chart that shows a method of tissue ablation by meansof a fluid cooled RF electrode, wherein RF is delivered in high-currentpulses that are terminated tissue boiling indicated by a rise inimpedance; wherein the inter-pulse duration of low signal output betweenpulses can increase during ablation process based on measurements of theablation process; wherein the amplitude of the high-current pulses areboth increased and decreased during the ablation process in response tomeasured parameters of the ablation process, and configured to stabilizethe pulse amplitude, pulse duration, and inter-pulse duration, and tomaximize the volume of ablated tissue; wherein the size of increases anddecreases in the amplitude of high-current pulses being varied duringthe ablation process.

FIG. 5 is a flow chart that shows a method of tissue ablation by meansof a high-frequency, internally-cooled ablation probe comprising:testing the function of the cooling system by measuring the electrodetemperature when coolant is flowing and the signal output level is low;setting the signal output to a high level configured to ablate, and thenfurther increasing the signal output level based on the tissue responseto the signal output; reducing the high signal output level to a lowsignal output level if boiling is detected in the tissue to allow forcooling of heated tissue over a cooling duration; varying the coolingduration during the ablation process in response to measured parametersof the ablation process; increasing and/or decreasing the high signaloutput level in response to measured parameters of the ablation process;alternating the signal output between the high output level and the lowoutput level until a termination criteria is reached.

FIG. 6 is a schematic diagram showing a circuit for a HF tumor ablationsystem including a HF power supply; a measurement circuit for the HFoutput level; a connection for at least one HF electrode including aswitch and measurement circuit for electrode current and temperature;connections for one or more ground pads each connection including aswitch and a measurement circuit for ground pad current; a coolant pumpconnected to the at least one electrode and including a measurement ofcoolant flow; a master controller capable of computing the power supplyoutput level, switch positions, and coolant flow rate in response tomeasured values and their history including HF output voltage, HF outputpower, impedance, electrode current, ground pad current, coolant flow,user interface state, user input, and functions of these values andother values; a controller configured to adjust the power supply outputlevel, switch positions, and coolant pump output level; a userinterface; a graphical display including numerical, digital, analog,and/or graphical displays of measured and computed values, anduser-interface elements.

FIG. 7 is a schematic diagram showing a system for high-frequency tissueablation that includes multiple cooled and non-cooled electrodes thatheat tissue at the same time; multiple ground pads that carry currentfrom the electrodes; an integrated nerve stimulator; a graphical displaythat includes a plot of output level, impedance, and temperature foreach electrode on one time axis; an integrated ultrasound imagingapparatus; display of US imaging data; controls for the an integratedultrasound imaging apparatus.

FIG. 8 is a schematic diagram showing a circuit for an RF generator thatincludes a RF power supply with a measurement circuit; a nervestimulation signal generator with a measurement circuit; connections tomultiple cooled electrodes and multiple non-cooled electrodes whereineach connection includes a measurement circuit for electrode current andtemperature, a switch configured to connect and disconnect the electrodefrom the reference potential, a switch configured to connect anddisconnect the electrode from the nerve-stimulation potential, a switchconfigured to connect and disconnect the electrode from the RFpotential; connections to multiple ground pads wherein each connectionincludes a measurement circuit for the ground pad and a switchconfigured to connect and disconnect the ground pad from the referencepotential; a coolant pump that delivers coolant to the cooledelectrodes; an ultrasound imaging machine; a controller that can measureand control the RF supply, stimulation signal generator, the switches,electrode current and temperature, ground pad current, coolant pumpoutput level, and ultrasound imaging parameters in response to systemprogramming and user input from the user interface; a user interfaceconfigured for monitoring and control of stimulation, tissue ablation,coolant pump, and ultrasound imaging machine; a graphical displayconfigured to display parameters and data for stimulation, tissueablation, and ultrasound imaging processes.

FIG. 9 is a schematic diagram that shows a medical system that includesan ultrasound imaging device and a high-frequency electrosurgicalgenerator that are both contained in the same chassis, and that are bothcontrolled by a single user interface console.

FIG. 10 is a schematic diagram showing a medical system configured tostimulate a nerve, record from a nerve, and ablate tissue at the sametime.

FIG. 11 is a schematic diagram showing the output signal delivered totwo electrodes energized by the same system, wherein the first electrodeis energized with a high-frequency signal configured to ablate tissue incontact with the first electrode, the second electrode is energized witha nerve stimulation signal, the high-frequency signal and the nervestimulation signal are not delivered at the same time, and returncurrent from the electrodes is carried by a ground pad.

FIG. 12 is a schematic diagram showing the electrical signal applied toeach of multiple electrodes energized in a monopolar configuration,wherein a high-frequency ablation signal and a stimulation signal areapplied to each electrode, current from the electrodes are carried bymultiple ground pads, the ground pads connected and disconnected fromthe generator reference potential in order to control a ground-padcurrent, no electrode is energized at the same time, and thehigh-frequency ablation signal source and the stimulation source areturned off during changes in the electrode and ground pad switch states.

FIG. 13 is a schematic diagram showing the electrical signal applied toeach of multiple electrodes energized in a monopolar configuration,wherein an RF ablation signal is applied to each electrode, current fromthe electrodes are carried by multiple ground pads, the ground pads areconstantly a generator reference potential, and no electrode isenergized at the same time.

FIG. 14 is a schematic diagram showing the electrical signal applied toeach of multiple electrodes energized in a monopolar configuration,wherein an RF ablation signal is applied to each electrode, current fromthe electrodes are carried by multiple ground pads, electrodes areenergized at the same time, and current from the electrodes is carriedby the ground pads alternately such that no ground pad carries currentat the same time.

FIG. 15 is a schematic diagram showing the electrical signal applied toeach of multiple electrodes energized in a monopolar configuration,wherein an single RF ablation signal is applied to multiple electrode atthe same time, current from the electrodes are carried by multipleground pads, and current from the electrodes is carried by the groundpads in a nested-simultaneous switching pattern.

FIG. 16 is a schematic diagram showing the electrical signal applied toeach of multiple electrodes energized in a sequential bipolarconfiguration, wherein at any given time, two electrodes carry returncurrents from the other without the use of a ground pad.

FIG. 17 is a schematic diagram showing the electrical signal applied toeach of multiple electrodes energized in a sequential monopolarconfiguration wherein only one electrode is energized at a time and aground pad carries return current from the electrode, and wherein and RFsignal and a stimulation signal is applied to an electrode at the sametime.

FIG. 18 is a schematic diagram showing the electrical signal applied toeach of multiple electrodes energized in a monopolar configurationwherein more than one electrode is energized at the same time multipleground pads carry return current from the electrodes, and wherein and RFsignal and a stimulation signal is applied to an electrode at the sametime.

FIG. 19 is a flow chart that shows a method for regulating theelectrosurgical current flowing through at least two ground padscomprising: switching the current among subsets of the ground pads;adjusting the pattern in which current is switched among subsets of theground pads; wherein more than one ground pad each carry a portion ofthe current at the same time.

FIG. 20 is a flow chart that shows a method for regulating a parameterof at least one of at least two electrosurgical ground pads comprising:switching the current among subsets of the ground pads in a patternhaving a timing and order of switch states; adjusting timing, order,and/or inclusion of switch states in the pattern; wherein the patternincludes at least one switch state in which a first ground pad carries afirst portion of the current, and a second ground pad carries a secondportion of the current, at the same time.

FIG. 21 is a flow chart that shows a method for regulating a parameterof each of at least two ground pads carrying return current from atleast one ablation electrode connected to a current source, comprising:producing a sequence of switch configurations, in each configuration ofwhich some or all ground pads are connected to the current source, andthe other ground pads are disconnected from the current source;measuring a parameter for each ground pad in each configuration;updating the order and timing of the switch configurations based on themeasurements.

FIG. 22 is a flow chart that shows a method for equalizing and reducingthe current flowing through each of at least two ground pads carryingreturn current from at least one ablation electrode connected to acurrent source, comprising: producing a sequence of switchconfigurations, in each configuration of which some or all ground padsare connected to the current source, and the other ground pads aredisconnected from the current source; measuring the current flowingthrough each ground pad in each configuration; updating the order andtiming of the switch configurations to equalize the RMS currents flowingthrough each ground pad based on the measurements.

FIG. 23 is a flow chart that shows a method for holding below a limitthe current flowing through each of at least two ground pads carryingreturn current from at least one ablation electrode connected to acurrent source, and for increasing the amount of time when more groundpads carry current at the same time, comprising: producing a sequence ofswitch configurations, in each configuration of which some or all groundpads are connected to the current source, and some ground pads aredisconnected from the current source; measuring the current flowingthrough each ground pad in each configuration; disconnecting a groundpad when its measured RMS current reaches the limit.

FIG. 24 is a flow chart that shows a method for control of a HF ablationprocess using an internally-cooled HF electrode, an automatedcontroller, ultrasound imaging of the ablation process, and a real-timegraphic display HF signal output parameters.

FIG. 25 is a schematic diagram showing, in three perpendicular views, anablation-probe guideblock including a cross-section having threebranches, at least one guidehole on each branch, and fiducial markersfor determination of guideblock position and orientation relative toanatomy in a medical image; wherein the guideholes are parallel holesthrough the guideblock; wherein the guideblock can be used to guide twoor more ablation probes, through two or more guideholes, into a body, inparallel, and in a linear, triangular, isosceles triangular, equilateraltriangular, or another type of configuration to influence the shape ofone or more ablation regions, to adapt to anatomical restriction, and/orto a suit clinical need; and wherein the guideblock has thin wallsaround the guideholes to reduce guideblock weight, to allow anultrasound transducer to be positioned close to the shafts of theablation probes at the surface of the body.

FIG. 26 is a schematic diagram showing a set of ablation-probeguideblocks, each including a cross-section having three branches, anablation-probe guidehole at the peripheral end of each branch, a centralalignment hole parallel to the ablation-probe guideholes; wherein thecentral axes of the guideholes of each guideblock are holes through theguideblock that are parallel to each other; wherein each guideblock canbe used to guide two or more ablation probes, through two or moreguideholes, into a body, in parallel, and in either a two-probe linear,or a three-probe equilateral triangular configuration; wherein the setof guideblocks provides for a variety of spacings betweenablation-probes.

FIG. 27A is a schematic diagram showing, in two perpendicular views, astackable ablation-probe guideblock having a mechanically-interlockfeature and an interlock release tab.

FIG. 27B is a schematic diagram showing a pair of stackableablation-probe guideblocks having complementary mechanical-interlockfeatures and interlock release tabs, wherein the guideblocks are shownin a mechanically-interlocked configuration; wherein the guideblocks areconfigured to guide two or more ablation probes through two or moreparallel guideholes, in parallel, into a body, in one of a variety ofparallel-ablation-probe configurations; wherein each guidehole is a holethrough the guideblock; wherein a user can push the guideblocks togetherto minimize the space they occupy, and the mechanical-interlock featuresare configured to help keep the guideblocks aligned and held together;and wherein a user can slide the guideblocks apart along one or moreablation probes already inserted through the guideblocks and into thebody, and then insert an additional ablation probe through correspondingguideholes in the guideblocks, thereby aligning the additional ablationprobe parallel to the already-inserted ablation probes over a distancelarger than the thickness of the guideblocks.

FIG. 27C is a schematic diagram showing a pair of stackableablation-probe guideblocks having complementary mechanical-interlockfeatures and interlock release tabs, wherein the guideblocks are shownin a separated configuration and are used in a method of aligningmultiple ablation probes in a parallel configuration, as the ablationprobes are inserted into a body.

FIG. 28 is a schematic diagram showing, in three perpendicular views, anablation-probe guideblock that can removed from ablation probes havinghubs that pass through the guideblock and into bodily tissue, withoutremoving the ablation probes from the bodily tissue; wherein theguideblock includes a cross-section having three branches, at least oneguide-slot on each branch; wherein each guide-slots is slot through theguideblock that is open at a side of the guideblock, that follows acircumferential path around a single common point in the guideblock andin a single common plane, and that has a semi-cylindrical referencesurface that is parallel to the semi-cylindrical reference surfaces ofthe other guide-slots; wherein the guideblock can be used to guide twoor more ablation probes, through two or more guide-slots, into a body,in parallel, and in one of a variety of linear or triangularconfigurations, by alignment of each ablation probe to asemi-cylindrical reference surface of a guide-slot; wherein theguideblock has thin walls around the guideholes to reduce guideblockweight, to allow an ultrasound transducer to be positioned close to theshafts of the ablation probes at the surface of the body; wherein thethickness of the guideblock is configured to be less than the minimumspacing between the semi-cylindrical reference surfaces of any twoguide-slots.

DETAILED DESCRIPTION OF THE INVENTION

FIG. 1 refers collectively to FIG. 1A, FIG. 1B, and FIG. 1C. FIG. 1presents schematically several embodiments of an apparatus for HFablation of tissue within a patient 190, in accordance with the presentinvention. Each of the embodiments in FIG. 1, include a HF generator 100such as an RF generator, a MW generator, or a RF and MW generator; oneor more ground pads 121, 122, 123, 124 applied to the skin surface ofpatient 190; one or more ablation probes 150, 160, 150A, 150B, 150C,placed within target anatomy, such as liver 193; a coolant pump 130 thatis configured to cool one or more of the ablation probes, eg 150; areservoir 135 for collection of used coolant; and an ultrasound machine140. The ground pads 121, 122, 123, and 124 can be connected to areference potential generated by the HF generator 100 to carry returncurrents from the ablation probe (150 in FIG. 1A, 160 in FIG. 1B) orprobes (150A, 50B, 150C in FIG. 1C). In some examples, the ground padscan be omitted when the HF generator 100 is delivering MW energy theablation probe. The at least one ablation probe can be connected to theHF output 116 of the HF generator 100. The coolant pump 130 can beoperably connected to the generator 100 by means of control connection134, and the activation and rate of coolant flow to an ablation probecan be controlled by the generator 100, for example, in coordinationwith ablation programs being run by the generator 100. The ultrasoundimaging machine 140 includes user controls 142 can be operably connectedto the generator 100 by means of control connection 144; controls 113included in the generator 100 can be used to operate some or allfunctions of the ultrasound machine 140; and controls 143 included inthe ultrasound machine 140 can be used to operate some of all of thefunction of the generator 100. A data file that includes procedure databoth from the RF generator and the ultrasound machine can be produced bythe combination of the generator 100 and the ultrasound machine 140;that data file can be saved to internally memory included in thegenerator 100; that data file can be saved to internal memory includingthe ultrasound machine 140; and that data file can be exported to anexternal data repository, such as an external disk or computer, by meansof a data connection included in the either the generator 100, theultrasound machine 140, or both. In some other embodiments, theultrasound machine 140 and generator 100 can be integrated into a singlehousing. In some other embodiments, the ultrasound machine 140 andgenerator 100 can be integrated into a single chassis with a singlescreen. The generator 100 includes a user interface, including agraphical display 101, which can be a touch screen and includesnumerical displays 104A, 104B, 104C, 104D, 104E, 104F, 104G, 104H andgraphical displays 102A, 102B, 102C, 102D, 102E, 102F, 102G, 102H, 119A,119B, 119C of readings and controls. The graphical user interface 101can graph readings, such as elapsed time, impedance, current,temperature, voltage, and power, as a function of time. In theembodiments shown in FIG. 1, The graphical displays 102A, 102B, 102C,102D, 102E, 102F, 102G, 102H, 119A, 119B, 119C each plot a parameter onthe vertical axis as a function of time on the horizontal axis, and caneach be referred to as an (x,y) line plot where y is time and x is aparameters selected from the list: impedance, current, power, voltage,and temperature. Each graphic display of a parameter can be color-codedso they are easy to discriminate from each other on the computer graphicdisplay 101. Each the digital and graphic display of the same reading,can have the same unique color, so that it is easy for the user toassociate the digital and graphic display of the same parameter, and todistinguish displays of different parameters. For example, impedancereading 104A can have the same color as graph 102C in FIG. 1A, and thatcolor can be green. The current reading 104B can have the same color asgraph 102A in FIG. 1A, and that color can be yellow. The temperaturereading 104D can have the same color as graph 102C in FIG. 1A, and thatcolor can be red. Other color assignments can be used. The generator 100includes one or more controllers for automated and/or semi-automatedcontrol of the HF output, including for example, control of the HFoutput as a function of a measured temperature, impedance, and the pastvariations of temperature and/or impedance. The generator 100 caninclude switches, controls, and programmed methods for control of thecurrent delivered to each pad, including the RMS current delivered to apad over a time period that is short relative to the time-constant ofthermal response of the ground pad.

The HF generator 100 can include a lamp 114 that indicates the activedelivery of HF energy capable of tissue ablation; a mechanical button108 by means of which a user, such as a medical doctor or nurse underthe direction of a doctor, can turn on the HF ablation output; amechanical button 109 by means of which a user can turn off the HFablation output; a mechanical knob 110 by means of which the user canadjust the output level of the HF ablation output, for example the HFcurrent, when the generator 100 is configured to allow for manualadjustment of the output; controls 113 for an ultrasound imaging machine140; one or more data connections 111, such as USB port or ports, thatcan each provide for transfer or data and/or control connection with oneor more of a computer network, an external hard disk, a computer, aflash drive, a wireless remote control, a wired hand controller, orprinter; a jack 116 that provides delivery of HF output to one or moreof an RF electrode, a MW antenna, a cluster of RF electrodes, or othertype of ablation probes; one or more ground pad jacks 115A, 115B, 115C,1115D for connection to one or more ground pads 121, 122, 123, 124; anda touch screen display 101. In some embodiments, the user can selectwhether the generator 100 delivers RF output, MW output, or both.

The generator can be capable of producing a high level of power,voltage, and current output, for example, a power output of 0 to 400 W,100 W, 200 W, 250 W, 300 W, 350 W, 400 W, or more than 400 W; forexample, a voltage output level of 100 to 200 Volts-RMS, 100 V-RMS, 120V-RMS, 140 V-RMS, 160 V-RMS, 180 V-RMS, 200 V-RMS, or more; for example,a current output level of 0-4000 mA-RMS, 500 mA-RMS, 1000 mA-RMS, 1500mA-RMS, 2000 mA-RMS, 2500 mA-RMS, 3000 mA-RMS, 3500 mA-RMS, 4000 mA-RMS,or more. In some embodiments, the generator 100 is an RF generatorcapable of producing 400 Watts and 3000 mA-RMS of RF output. An outputlevel of up to 400 W and/or up to 3000 mA-RMS is advantageous forheating cooled RF electrodes with shaft diameters in the range 18-14gauge and tip lengths in the range 1 to 6 cm, both in single-electrodeand in multi-electrode cluster configurations.

The generator 100 can store all measured readings during, before, andafter running an ablation program to memory as a procedure record fileor files. The record file can be stored in memory internal to thegenerator and to external memory, such as an external disk attached todata port 111. The procedure record can include averages, maximum,modes, and other statistics of measured readings configured to providethe physician with a meaningful, easy to understand record of a medicalablation procedure. The procedure record can include or be processed toproduce graphs and analysis of measured values. The procedure record caninclude text annotation of the data, including patient information. Insome embodiments, the generator can explicitly prevent the storageexport of sensitive patient information in the procedure record. Theprocedure record can include ultrasound, fluoroscopy, CT, MRI, and otherimaging data.

In some embodiments, an interface between a HF generator 100 andultrasound machine 140 via connection 144 can be standardized to allowfor interoperability different HF generators and different ultrasoundmachines. In one example, the manufacturer of the generator 100 canwrite a specification for data connection 144, and provide a technicalspecification for the data connection 144 to one or more manufacturersof US machines (such as ultrasound machine 140), whereby each of thesaid one or more manufacturers of US machines can construct a US machineconfigured to inter-operate with the generator 100. A method of salesand marketing for a tissue ablation apparatus 100 comprises including aninterface 144 in the tissue ablation apparatus 100 and publishing aspecification of that interface. This solves the problem of how tointegrate tissue ablation technology from a one manufacturer withmedical imaging technology from another manufacturer or manufactures. Insome examples, the specification can be provided publically. In someexamples, the specification can be provided privately. In some examples,the specification can be provided for free. In some examples, thespecification can be provided for a price. The specification for thedata connection 144 can include pin outs, signal levels and limits,command codes, timing specifications, and other specifications familiarto one skilled in the art of communication and control. The interface144 can carry multiple type of a data, including data for control ofoperations of the generator 100, data for control of operations of theUS imaging system 140, data representing operation and measurements ofthe HF electrosurgical apparatus 100, data representing operation andmeasurements of the US imagining machine 140. For example, thespecification can explain how an US machine 140 (or another type ofdevice) can perform one or more of the following functions by means ofthe connection 144: read the signal output level measurements of thegenerator 100, read the impedance measurements of the generator 100,read the timer of the generator 100, read the temperature measurementscollected by the generator 100, read the settings of the generator 100,read patient and physician data from the generator 100, read theoperational state of the generator 100, read images displayed on thescreen of the generator 100, enable and disable the signal output of thegenerator 100, change the settings of the generator 100, change theoperational state of the generator 100, send image data from the USmachine 140 to the generator 100, send imaging settings to the generator100, send to the generator 100 operational state information about theUS machine 140, allow the generator 100 to control the operational stateof the US machine, allow the generator 100 to adjust the settings of theUS machine 140, allow the generator 100 to read patient and physiciandata from the US machine 140. The specification can be used to verifyand validate the inter-operation of an US machine 140 and ablationapparatus 100. In some embodiments, the data connection 144 include oneof the communication types selected from the list: USB, serial,parallel, RS232, VGA, HDMI, DVI, or a custom communications protocol. Insome examples, the communication connection 144 can be uni-directional,such as wherein data is sent from the generator 100 to the US machine140, or wherein data is sent from the US machine 140 to the generator100. In some examples, the communication connection 144 can bebi-directional, wherein data is sent back and forth between theelectrosurgical system 100 and the ultrasound imaging apparatus 140. Insome embodiments, the ultrasound imaging apparatus 140 can be anothertype of medical imaging apparatus, including, without limitation, afluoroscopy imaging apparatus, an x-ray imaging machine, an MRI scanner,a CT scanner, a spiral CT scanner, a PET scanner, an optical coherencetomography (OCT) device. In some embodiments, the medical apparatus 100can be another type of diagnostic or interventional medical device,including, without limitation a RF generator, a MW generator, a laserablation device, an irreversible electroporation (IRE) ablationapparatus, a cryo-ablation device, an optical coherence tomography (OCT)imaging device.

In another example, the manufacturer of the ultrasound machine 140 canwrite a specification for data connection 144, and provide a technicalspecification for the data connection 144 to one or more manufacturersof HF generators (such as generator 100), whereby each of the said oneor more manufacturers of HF generators can construct a HF generatorconfigured to inter-operate with the ultrasound machine 140. A method ofsales and marketing for a medical imaging apparatus 140 comprisesincluding an interface 144 in the medical imaging apparatus 140 andpublishing a specification of that interface. This solves the problem ofhow to integrate tissue medical imaging technology from a onemanufacturer ablation technology from another manufacturer ormanufactures. In some examples, the specification can be providedpublically. In some examples, the specification can be providedprivately. In some examples, the specification can be provided for free.In some examples, the specification can be provided for a price. Thespecification for the data connection 144 can include pin outs, signallevels and limits, command codes, timing specifications, and otherspecifications familiar to one skilled in the art of communication andcontrol. The interface 144 can carry multiple type of a data, includingdata for control of operations of the generator 100, data for control ofoperations of the US imaging system 140, data representing operation andmeasurements of the HF electrosurgical apparatus 100, data representingoperation and measurements of the US imagining machine 140. For example,the specification can explain how an ablation apparatus 100 (or anothertype of device) can perform one or more of the following functions bymeans of the connection 144: read the operational state of the USmachine 140, read the measurements of the US machine 140, read thesettings of the US machine 140, read patient and physician data from theUS machine 140, read the operational state of the US machine 140, readimages displayed on the screen of US machine 140, enable and disable thefunctions of the US machine 140, change the settings of the US machine140, change the operational state of the US machine 140, send signaloutput and measurement data from the generator 100 to the US machine140, send generator settings to the US machine 140, send to the USmachine 140 operational state information about the ablation apparatus100, allow the US machine 140 to control the operational state of thegenerator 100, allow the US imaging device 140 to adjust the settings ofthe generator 100, allow the US machine 140 to read patient andphysician data from the generator 100. The specification can be used toverify and validate the inter-operation of an US machine 140 andablation apparatus 100. In some embodiments, the data connection 144includes one of the communication types selected from the list: USB,serial, parallel, RS232, VGA, HDMI, DVI, or a custom communicationsprotocol. In some examples, the communication connection 144 can beuni-directional, such as wherein data is sent from the generator 100 tothe US machine 140, or wherein data is sent from the US machine 140 tothe generator 100. In some examples, the communication connection 144can be bi-directional, wherein data is sent back and forth between theelectrosurgical system 100 and the ultrasound imaging apparatus 140. Insome embodiments, the ultrasound imaging apparatus 140 can be anothertype of medical imaging apparatus, including, without limitation, afluoroscopy imaging apparatus, an x-ray imaging machine, an MRI scanner,a CT scanner, a spiral CT scanner, a PET scanner, an optical coherencetomography (OCT) device. In some embodiments, the medical apparatus 100can be another type of diagnostic or interventional medical device,including, without limitation a RF generator, a MW generator, a laserablation device, an irreversible electroporation (IRE) ablationapparatus, a cryo-ablation device, an optical coherence tomography (OCT)imaging device.

Referring now to FIG. 1A, the HF system comprises a HF generator 100that is adapted to measure the generator signal output parametersincluding one or more of parameters from the list of impedance, power,current, and voltage. The graphic computer in system 100 is adapted tographically display in real time these signal output parameters on thegraphic display 101. The effects of modulation of the signal output onthe measured parameters to stabilize the ablation process when theprocess is pushed into the limit of an explosive bubble zone can bevisualized on the computer graphic display 101. This aspect is shown inmore detail in the figures that follow.

In FIG. 1A, the graphical plot of parameters 102A, 102B, 102C gives theclinician a visual, intuitive, and real time update and evaluation ofwhether the ablation process is proceeding properly and safely. In oneexample, the graph 102A can represent signal output current. In oneexample, the graph 102A can represent signal output power. In oneexample, the graph 102A can represent signal output voltage. The dottedgraph 102B represents schematically the output impedance. The upwardspikes in impedance, such as spike 118, represent the occurrence ofboiling and bubble formation in the tissue around the active or exposedtip of the ablation electrode 150. The bubble zone is the hottest regionaround the electrode active tip 151 and is located at a distance fromthe electrode tip 151, which is cooled. This is an unstable situation.If the generator signal output is not reduced, the bubble zone willexplosively expand, the impedance spike will shoot up, and the ablationcurrent and power will be reduced dramatically. This unstable situationcan be avoided by quick reduction of the generator signal output beforethe impedance spikes reach too high a level. That impedance level can bea threshold set point in the control system that can be set by theclinician or the manufacturer. That impedance level can be the triggerpoint to reduce the generator signal output, as illustrated by thereduction from a high level 118A to a low level 118B in graph 102A. Inone example, the signal output is reduced to zero for a down time 118Baccording to the generator controller. In another example, the signaloutput is reduced or modulated to non-zero value in the down time 118Baccording to the controller. The down time 118B allows the bubble zoneto cool down and the bubbles to dissipate and the impedance to reduce toa baseline value as shown during down time 118B in graph 102B in FIG.1A. Then the signal output, in one example, can be again brought up to ahigher level for another up time, as shown by the level 118D. Theablation heating process resumes during the up time, and the signaloutput current can pass through the bubble zone and heat the tissueoutside it to continue enlarging the ablation size. Then in one example,the signal output level in the up time will heat and grow the bubblezone again so that after an up time duration the impedance will onceagain become unstable and spike upward. The up time duration depends onthe upper signal output level during the up time. In one example, thesignal output level will again be turned off for a down time durationaccording to the control system and programmed methods. The repeatingprocess of up times (eg 118A) and down times (eg 118B) continuesaccording to the automatic controller. The process can, in one example,stabilize to a desired level of signal output level during the up timesand a desired repeating durations of up times and down times to producea desired ablation process and ablation size. In one example, thecontrol system uses the level of impedance spikes (eg 118) and thesignal output levels to stabilize the sequences of up times and downtimes so that the ablation process is uniform and reproducible for agiven electrode geometry and tissue impedance. In another aspect thetotal duration of the ablation process has an effect on the ablationsize. This can be a parameter in the controller to predict desiredablation size. The ablation size can be reproducible and predictable bystabilizing the above described control process.

A very important and useful advantage for the clinician is to have aninstant and intuitively clear visual check and feedback on the stabilityand control of the ablation process as it proceeds. One example of howto provide that is to provide a computer graphic real time display ofthe generator signal output during the procedure. In one example, thegraph of only one of the generator signal output parameters, power,current, or voltage, is displayed on the computer graphic display 101.In the example that the displayed parameter is power and/or current, theup times and down times, as well as the stability of the power and/orcurrent level, can visually tell the clinician at a glance if theablation process is going stably as executed by the controller, or ifthe ablation process is going wrong. In one example, if the up-timepower and/or current is too high, then excessive boiling will occur inthe bubble zone. The impedance will be sustained at too high levels, andthe power and/or current graphic display 102A will slump, decrease, orotherwise become erratic or unstable. In one example, the displayedoutput parameter is voltage, and excessive voltage levels during the uptime periods will cause impedance 102B to be sustained at too highlevels causing the voltage to rise or fall or otherwise behave erraticand not according to smooth desired behavior. In another example, wronglevels of the displayed generator signal output parameter can cause theautomatic controller to produce incorrect, erratic, or unstabledurations of the up times and/or down times, indicating a deviation froma desired ablation process. These and other examples can be visualizedand instantly and intuitively accessed by the clinician by the graphicreal time display 102A of one or more of the signal output parameters inthe list of power, current, and voltage. This gives the advantage ofsafety and control.

In one example, the signal output impedance 104A, 102B is measured bythe control system. The level and timing of the upward impedance spikes,such as 118, is also measured, and the control system uses thatinformation to determine the timing and/or durations of the up times anddown times and/or the levels of the signal output parameters, as theablation process goes along. In one example, the impedance 102B is notdisplayed on the computer graphic display, but processing of theimpedance information is done within the control system according to theautomatic controller. The results of the processing is indirectlymanifest in the graphic display of the one or more signal outputparameters 102A. Another advantage of the real time display of one ormore signal output parameters 102A is that it gives the clinician aninstant check of the working of the control system and programmedprocesses.

In another example the impedance 102B is displayed on the computergraphic display along with the display of the one or more signal outputparameters 102A. The graphic displays of impedance 102B and the one ormore output parameters 102A can be stacked on each other and/or overlaidrelative to the same time scale also displayed on the same computergraphic display 101. This is illustrated in FIG. 1A by the impedancegraph 102B. This enables the clinician to see the impedance spikes, suchas 118, and see that the level to which they rise is within desiredlimits according to the automatic controller. One advantage is theclinician can visually evaluate the relation of impedance behavior 102Band behavior of the one or more signal output parameters 102A to see ifthe control system and control process are functioning properly.

Also shown in FIG. 1A are digital displays of the power 104F, current104B, voltage 104E, impedance 104A, and elapsed time 104C. In oneexample, as shown in FIG. 1A, the current to each of the surface groundpads are shown digitally 103A, 103B, 103C, and 103D. In anotherembodiment, a plot of each of the ground pad currents over time isadditionally shown on display 101. For example, element 103 can includea line graph plotting each ground pad current on the vertical axis andtime on the horizontal axis; in some embodiments, the horizontal axiscan have the same time scale as that of the electrode plots 102A, 102B,102C. If one or more of the ground pads is lifting off the skin or isotherwise separated, then the graphic display of current for that padwill show an anomaly, for example, as a dip of discontinuity in thegraph. In some embodiments, the impedance of each ground pad can bedisplayed digitally and/or graphically. One advantage of graphic and/ordigital displays of ground pad current and/or impedance is that theygive the clinician and instant warning of trouble with the equipment toavoid harm to the patient such as skin burns.

FIG. 1A also shows graphic user interface controls, including buttons105, 106, and 107. In one example, these controls include interactionwith the automatic controller and computer graphic control to adjustparameters of the ablation process to suit the clinician needs.

The present invention has the advantage of producing reproducibleresults in terms of ablation zone size. Visual graphic display of outputparameters during the ablation process and seeing that the parametersare stable can indicate to the clinician uniformity of control from onepatient to another and one target situation to another. This issignificant because the ablation process is a repetition of approachinga unstable boiling condition. Bringing stability to this unstableprocess and enabling visual conformation is a significant advantage.

Referring to FIG. 1A, FIG. 1A is a schematic drawing showing one exampleof an arrangement of an apparatus for performing HF ablation of bodilytissue relative to the patient 190, in accordance with some aspects ofthe present invention. A cooled HF electrode 150 is inserted into thepatient body 190 percutaneously. The ablation electrode 150 includes ahub 153 at the electrode proximal end, and an elongated shaft portionwith a distal end and a proximal end, wherein the distal end is insertedinto the patient body 190 percutaneously, and wherein the shaft portionincludes an insulated portion 152 and a tip portion 151. In one example,the shaft portion can comprise rigid metal tubing which is insulated onits outside surface on the insulated portion 152 and uninsulated onactive tip portion 151. In another example, the shaft portion is aflexible structure having uninsulated tip portion 151. In anotherexample, the tip portion 151 can comprise an antenna structure forpropagating MW energy into body tissue. The electrode is adapted toconnect to the HF system 100 by attaching electrode cable 154 togenerator jack 116. The HF system 100 comprises a HF generator of HFsignal output, a control system with an master controller configured tocontrol the ablation process, and a computer adapted to give a computergraphic display 101 of parameters of the ablation process. Connection116 is adapted to carry HF power from the HF generator 100 through theelectrode tip 151 to produce an ablation volume 194 within a targetstructure or structures 193 within the body 190. In some examples,target structure 193 can be an organ such as the liver, lung, kidney,brain, nerve, bone, vertebra, uterus, prostate, or a tumor within anorgan. As a schematic example in FIG. 1A, a target organ 193 can have atumor within it, and the operator of the ablation apparatus desires theablation volume 194 to cover and destroy the tumor.

In the embodiment shown in FIG. 1A, the ablation probe 150 includes aninternally-cooled RF electrode 150E inserted into a tissue-piecing RFcannula 150U, wherein the internally-cooled RF electrode 150E includeshub 153B connected to cable 154 and tubes 155 and 156, andinternally-cooled shaft 152B with blunt distal end 151B; wherein thecannula 150U includes hub 153A, insulated proximal shaft portion 152,and distal active tip 151; wherein both the electrode 150E and thecannula 150U can be provided sterile-packed to the user. Electrode hub153B inserts into and engages with cannula hub 153A to form the ablationprobe hub 153, and to the set the relative positions of the cooledelectrode shaft 152B, cannula shaft 152, and active tip 151, such thatthe electrode shaft 152B cools the active tip 151, and the electrodedistal end 151B is aligned with the bevel of the cannula active tip 151.The thickness and material of the internally-cooled electrode shaft 152Band blunt distal end 151B (eg thin-wall strainless steel hypotube with athin-wall closed distal end), the thickness and material of the cannulashaft 152 and active tip 151 (eg thin-wall strainless steel hypotubecovered by a thin layer of electrical insulation in shaft portion 152),the fluid flow rate through the shaft 152B produced by pump 130 (eggreater than 70 mL/min, or preferably 100 mL/min or greater), and thetemperature of the fluid flowing through shaft 152B (eg 0-30° C. or0-15° C.) are all configured to provide for cooling of the bodily tissue190, 193 in contact with the active tip 151 to enhance the size oftissue ablated by the ablation probe 150 when energized by generator100. The engagement surface 153C of electrode hub 153B is shown withincannula hub 153A as a dotted line. In one example electrode hub 153B canbe a male luer hub, and cannula hub 153A can be a female luer hub. Theelectrode shaft 152 is shown as a dotted line within the lumen of thecannula shaft 152 and active tip 151, and the distal end of theelectrode shaft 151B is positioned at, or slightly beyond, the hole inthe flat sharp bevel at the distal end of the active tip 151. In someexamples, the electrode point 151B can be flush with the bevel of thecannula tip 151. In some examples, the electrode point 151B can bealigned with the center of the bevel of the cannula tip 151. In someexamples, the curved part of the electrode point 151B can be just distalto the distal-most point of the tip 151 to form a substantially roundedcombined active tip to reduce peak electric fields at points of highcurvature, and to reduce heat accumulation in tissue just distal to thedistal end of the ablation probe 150. The electrode shaft 152B caninclude a metallic outer surface that touches an inner metallic surfaceof the cannula shaft 152 and/or active tip 151 to provide RF outputsignal from the electrode to the active tip 151. The cannula active tip151 includes echogenic markers 151A configured to produce an enhancedimage of the active tip 151 when viewed using ultrasound imaging, asshown on ultrasound display 141. In one example, the echogenic marketers151A can be depressions in the outer surface of the metallic active tip151, arrayed around and along the active tip 151, having a substantiallyflat bottom in the wall of the active tip, and having isoscelestriangular cross-section in a plane roughly parallel to the cylindricalouter surface of the tip 151, wherein one altitude of the triangularcross-section is parallel to the long axis of the tip 151 and shaft 152,and wherein the vertex of the triangular cross-section through which thealtitude passes is closer to the distal point of the tip 151 than is thebase side of the triangular cross-section to which the altitude isperpendicular. In this example, the two distal side faces of eachtriangular marker provide reflective surfaces for incoming ultrasoundwaves, the open space within each depression allows ultrasound wavesaccess to the two distal side faces, and the triangular cross-sectionallows more markers to arranged longitudinally along the active tiprelative to depression having a diamond- or square-shaped cross-sectionof the same width in the cannula circumferential direction. In oneexample, each of the echogenic markers 151A can have extent of0.001-0.020 inches the longitudinal direction of tip 151, a 0.001-0.020inches in circumferential direction of the tip 151, and depth of0.001-0.006 inches in the tip wall (ie the tip radial direction). Insome examples, the triangular cross-section flat-bottom depression canform a corner-cube reflector. In some examples, the echogenic markers151A can take other forms, such as circular flat-bottom depressions,square flat-bottom depressions, diamond flat-bottom depressions,arbitrary triangular flat-bottom depressions, hemispherical depressions,corner-cube depressions, holes through the side of cannula shaft 151,152, roughing of the cannula shaft surface, sand-blasting of the cannulashaft surface, knurling of the surface, and combinations of these andother echogenic features in either identical or varied orientations. Insome examples, echogenic markers 151A can be included in a metal surfaceunder the electrical insulation of the insulated proximal shaft 152. Insome embodiments, other arrangements of echogenic markers 151A can beincluded on probe 150 to highlight different features and dimensions ofthe probe 150. In some embodiments, the entirety of the cannula shaftlength 151, 152 can include echogenic features. Before insertion of thecannula 150U into the patient tissue 190, a stylet 150S can be insertedto the inner lumen of the cannula shaft 152 and tip 151 (with theelectrode 150E removed from the lumen) to close and align with the holein the distal bevel of the active tip 151 and thereby form a solid beveltip, wherein the stylet 150S includes a hub 153D, shaft 152D with distalbevel point 151D; this configuration provides for smooth insertion ofthe cannula 150U into the patient body 190 and organ 193, in partbecause the cannula 150U and stylet 150S combination includes a sharp,substantially solid bevel, and a smooth, cylindrical outer shaft havingsubstantially the same cross-section along its entire length, withoutany step discontinuities between the cannula 150U and the stylet 150Souter diameters that could catch onto and thereby displace bodilystructures within patient 190 during insertion. The alignment of thestylet 150S and cannula 150U bevels to form a smooth bevel and a smoothouter shaft surface is an advantage of the embodiment of thecannula-electrode ablation probe 150 shown in FIG. 1A. Smooth insertionof an ablation probe can be important to avoid displacing the organ 193,target anatomy such as a tumor, and other bodily structures duringinsertion of the probe. For example, tissue displacement can be morelikely to happen if the target organ 193 is a cirrhotic liver thatincludes a hepatocellular carcinoma (HCC) tumor, because a cirrhoticliver can more tough and harder to push through than a healthy liver.Avoiding displacement of soft-tissue anatomy, such as an organ 193 suchas the liver, can be especially important when using ultrasound guidancein relation to pre-operative three-dimensional (3D) medical images (egCT, MRI, PET) for placement of the probe 150 because movement of thetarget anatomy intra-operatively can make the pre-operative imaging lessaccurate. Displacement of an organ can be more likely to occur if theablation probe has a changing cross-section along its shaft, such as onethat includes catch-points along its outer surface; this can occur whena cannula shaft has a square-cut end from which a thinner styletprotrudes. The ablation probe 150 is directed toward the problem ofproviding both a lumen for injection of fluids, for a smooth externalablation probe surface, for cooled RF ablation of tissue, and forultrasound guidance. In the embodiment shown in FIG. 1A, once thecannula is in position in the patient body 190, then the stylet isremoved from the cannula inner lumen, and the internally-cooledelectrode is inserted into cannula inner lumen to form cooled RFablation probe 150. The distal end of the electrode 151B issubstantially aligned with the distal bevel of cannula tip 151A, and thelength of the electrode shaft 152B is substantially the same length asthe stylet shaft 152D; this has the advantages that include: the cannulaprovides a fixed channel within the body 190 into which the stylet andelectrode can be exchanged; injections can be introduced into the bodythrough the cannula lumen at the distal end of the active tip 151 forfluid ablation, lesion size enhancement, perfusion ablation, antibioticinfusion, infusion of biologics, and/or anesthesia; the stylet does seedtumor cells to positions distal to the active tip that might not beablated by the heat lesion that forms around the active tip; and tissueis not mechanically damaged by penetration distal to the active tip. Insome embodiments, the ablation probe 150 can be the ablation probesystem shown in FIG. 2 of U.S. patent application Ser. No. 13/153,696.In some embodiments, the ablation probe 150 can be the ablation probesystem shown in FIG. 2A, 2B, and 2C of U.S. patent application Ser. No.14/072,588. In some embodiments, the ablation probe 150 can be theablation probe system shown in FIG. 2D of U.S. patent application Ser.No. 14/072,588. In some embodiments, the ablation probe 150 can be partof the ablation probe system shown in FIG. 2E of U.S. patent applicationSer. No. 14/072,588. In some embodiments, the ablation probe 150 can bepart of the ablation probe system shown in FIG. 2F of U.S. patentapplication Ser. No. 14/072,588. In some embodiments, the ablation probe150 can be the ablation probe system shown in FIG. 2I and 2J of U.S.patent application Ser. No. 14/076,113. In some embodiments, theablation probe 150 can be the ablation probe system shown in FIG. 2K,2L, and 2M of U.S. patent application Ser. No. 14/076,113.

The cooled RF ablation probe 150 shown in FIG. 1A, both on its own andas part of the electrosurgical system presented in FIG. 1A, hassubstantial advantages and simultaneously solves numerous problems oftissue ablation. The combination of a cannula and electrode to form anablation probe 150 provides a fluid channel for fluid injection into theablation site, for example, for injection and/or perfusion of an ionicfluid to enhance lesion size, injection of ablation fluid to kill tumorcells, injection of anesthetic to numb pain, and/or injection ofantibiotics to prevent infection; this is not provided by solid-tipablation probes. The stylet and the electrode do not substantiallyprotrude from the hole at the cannula distal end 151; this hasadvantages that include: the external surface of the combined ablationprobe 150 is smooth, without any discontinuities, steps, or othertransitions in cross-section size or shape (which can be present whenthe stylet and/or electrode protrudes from a square cannula distal end,even with the transition is tapered), thus reducing insertion forces andthe likelihood of displacing soft tissue and organs during insertion andmanipulation (eg when inserting a probe into tough cirrhotic liver toablate an HCC tumor) and thus potentially making pre-operativethree-dimensional (3D) imaging data (eg CT, MRI, PET) less easy torelate to intra-operative anatomy as visualized with ultrasound imaging141; the electrode 150E is not substantially inserted into bodilytissue, thereby reducing the force applied to the electrode 150E, andthereby avoiding the need for large and/or heavy means to make theelectrode 150E more robust (such as a large and/or heavy handleconfigured for pushing the electrode 150E) which can prevent closespacing of multiple ablation probes (for example, in a clusterconfiguration, eg 150A, 150B, 150C of FIG. 1C) and which can displace anprobe position in bodily tissue either before or during ablation due totorque from the weight of the portion of the probe and hub that remainsoutside the body; fluids injected to enlarge lesion size (such as salineand other ionic solutions), either before the lesion or during thelesion as an ongoing infusion, are injected at the point of greatestheat around the active tip 151 (ie the distal point of the active tip151), thereby reducing maximal tissue temperatures and tissue boilingthat can limit delivery of RF energy to the tissue 190; fluids injectedto kill cancer cells (such as alcohol), anesthetics, steroids, and/orantibiotics can be delivered over the full length of the active tip 151without advancing the cannula 150U and thus potentially seeding cancercells to healthy tissue, either by injecting ablation fluid as thecannula 150U is withdrawn from the patient 190 or by the inclusion ofside holes along the active tip 151 which can themselves be echogenic;the interface between the tissue and the external surface of theablation probe 150 does not substantially change when the electrode 150Eand stylet 150S are inserted into and removed from the cannula 150U,thereby minimizing tissue movement which can make pre-operative imagingdata less useful; the stylet 150S does not penetrate into tissue distalto the distal position of the electrode 150E and cannula active tip 151,thereby reducing the likelihood of movement of cancer cells to thelocation of healthy tissue that is not ablated by the active tip (aprocess known as “seeding”). The stylet distal end 151D can be matchground to the distal bevel of the cannula tip 151 to produce a solid,sharp bevel that reduces tissue coring and resistance during probeinsertion, thereby reducing the need for a heavy and/or large hub handlewhich can prevent close spacing of multiple probes in a cluster (eg FIG.1C) and displace the position of an ablation probe placed in bodilytissue. A single internally-cooled electrode 150E can be used to operatea variety of cannulae like cannula 150U; advantages of this include: asingle electrode 150E (which is generally more expensive than a cannula150U) can operate with a variety of cannula types having differentactive tip lengths, thereby reducing stocking costs and logistics forphysicians relative to the use of integral ablation probes (such as theRadionics Cool-Tip) for which a variety of electrodes having a varietyof active tip lengths are kept in supply into order to adapt to clinicalneeds as an ablation procedure progresses; and multiple cannulae likecannula 150U can be placed at multiple positions in the patient body atlow cost and without encumbrance from multiple sets of electrode tubing(eg 155, 156) and cables (eg 154), the multiple cannulae can bevisualized relative to each other before lesioning (for example usingultrasound or three-dimensional imaging), and then either lesioning canbe performed at each cannula using a single electrode 50E bysequentially moving the electrode 150E among the cannulae (thus keepingcost low), or each of multiple cannula can be energized with one ofmultiple electrodes. The cooled electrode 150E including a cable 154 andcoolant tubes 155, 156 is physically separate from the cannula 150U; theadvantage of this configuration include the ability to easily positionmultiple ablation probes in a variety of locations within the body 190at the same time (including in a tight cluster configuration, like thoseshown in FIG. 1C) without the encumbrance of cables and coolant tubesduring placement. This advantage can be especially important for usewith an RF generator capable of energizing multiple ablation probes atthe same time (eg generator 100 as shown FIG. 1C, generator 200 as shownin FIG. 2, generator 700 in FIG. 7, and generator 900 in FIG. 9) andwith ultrasound guidance because one hand of physician is generallyoccupied holding the ultrasound transducer. The electrode distal tip151B can have a thin-wall and rounded distal end, which increasesthermal conduction of heat from the tissue into the internally coolant,and reduced electric field strengths relative to sharp-point electrodes,thereby cooling tissue distal to the ablation probe 150, which is thelocation where tissue temperatures can be hottest and thus limit lesionsize. Echogenic markers 151A of the ablation probe 150 identify theactive tip 151 (and can identify other features and dimensions), whichcan facilitate injection and ablation using ultrasound guidance.

In some embodiments, the ablation probe 150 can be an RF electrode. Insome embodiments, the ablation probe 150 can be an MW antenna. In someembodiments, the ablation probe 150 can be an integral, tissue-piercingRF electrode. In some embodiments, the ablation probe 150 can be acooled-RF electrode 150E that is inserted into a tissue-piercing cannula150U. In some embodiments, the ablation probe 150 can be one of theablation probe systems presented in U.S. patent application Ser. No.13/153,696. In some embodiments, the ablation probe 150 can be one ofthe ablation probe systems presented in U.S. patent application Ser. No.14/072,588. In some embodiments, the ablation probe 150 can be one ofthe ablation probe systems presented in U.S. patent application Ser. No.14/076,113. In some embodiments, the ablation probe 150 can additionallyinclude an extension tip temperature sensor, such as that shown in FIG.2G and 2H of U.S. patent application Ser. No. 14/072,588.

In another example of FIG. 1A, there can be more than one ablation probesimilar to 150 inserted into the target organ 193 to create a largerablation volume 194. In some embodiments, the more than one ablationprobe can be connected to the HF generator signal output at the sametime; this configuration can be referred to as a cluster configuration.In some embodiments, multiple electrodes energized in a clusterconfiguration can be position close to each other to produce a singlelesion volume; in some embodiments, the single lesion volume can be anenlarged coherent volume, and in some embodiments, the single lesionvolume can be not enlarged, but having an irregular shape conforming totarget anatomy. In some embodiments, multiple electrodes energized in acluster configuration can be positioned far from each other to producemultiple lesion volumes. In some embodiments, the more than one ablationprobe can be connected to the HF generator signal outputnon-concurrently; this configuration can be referred to as amultiple-electrode monopolar configuration.

FIG. 1A shows schematically one example of a coolant supply system 130to cool the active tip portion 151. A reservoir 132, in one example,contains water or saline cooled to a temperature less than bodytemperature, such as room temperature, approximately 20 deg C., nearfreezing, less than 10 deg C., or near 0 deg C. Tubing 155 carries thecoolant through a peristaltic pump head 131 that pumps the coolantthrough the electrode 150E, and thus the ablation probe assembly 150.The electrode 150E has an internal channel through which coolant canflow to cool the probe active tip 151 when the electrode 150E isinserted in cannula 150U. The coolant can exit the probe 150 throughtubing 156 and dump into the collection reservoir 135. The pump 130 alsoincludes a user control 133 to provide for manual control of pumpfunction. The generator 100 provides an automatic check on the coolantflow into the electrode 150E and ablation electrode 150 when an ablationprogram is initiated by the user by holding the output level at a lowlevel not expected to heat the electrode tip 151 even in the absence ofcooling for an initial period 118C visible on output level graph 102A,and only proceeding with ablation output if the electrode temperature,plotted by dotted line 102C, registers a value below a thresholdindicative of proper electrode cooling, such as a temperature below 30deg C. In some embodiments, the generator 100 does not proceed withablation heating unless the temperature first registers a valueindicative of body temperature, and then drops to a value indicative ofcoolant flow. In some embodiments, the generator 100 can discontinue theablation program and signal an error condition to the user, if thecoolant-check period 118C persists for longer than the typical timerequired for coolant to flow from the reservoir 132 to the electrode tip151, for example 20-45 seconds depending on the pump rate. In someembodiments, the coolant check can be performed on an ongoing basis whenablation generator is being delivered to verify that the coolant flow issufficient for the ablation output level delivered. In some embodiments,the generator 100 automatically activates the coolant pump viaconnection 134 when the user initiates an ablation program, for example,by pressing the Start button 108. In some embodiments, for example whereconnection 134 is absent, the user manually activates by control 133 thecoolant pump to suit clinical needs.

The HF system comprises a HF generator 100 that is adapted to measureparameters of the ablation signal output delivered to the ablation probe150 or probes, including one or more of parameters from the followinglist: impedance, power, current, voltage, and functions of the timesignals of one or more of these parameters. The graphic computer insystem 100 is adapted to graphically display simultaneously in real timeone or more of these signal output parameters on the graphic display101. In one example, the graphical display can be one or more signallines 102A, 102B, or 102C plotted over time, each with the parameterplotted on a vertical axis and time plotted on a horizontal axis. Thegenerator 100 can be capable or modulating the HF output level,including turning the HF output on and off, in response to measured HFsignal parameters. In some embodiments, the modulation of the HF signaloutput can be configured to stabilize the ablation process, for example,to prevent or reverse the effects of boiling tissue around the activetip 151. The computer graphic display 101 can present to the user visualinformation about the effect of modulating the HF signal output when theablation process produces tissue boiling and an explosive bubble zonearound the active tip 151. This aspect of the present invention is shownin more detail in the figures that follow.

Also shown in FIG. 1A are ground pads 121, 122, 123, 124 which areconnected to jacks labeled “G1”, “G2”, “G3”, “G4” of generator 100,respectively. In this example, pad 121 is applied to the posterior sideof a muscular portion of left thigh 192, pad 122 is applied to theanterior side of a muscular portion of left thigh 192, pad 124 isapplied to the posterior side of a muscular portion of right thigh 191,pad 123 is applied to the anterior side of a muscular portion of rightthigh 191. Each ground pad is connected to an individual jack ongenerator 100 and adapted to carry return HF current from the active tip151 of cooled HF electrode 150 back to the generator 100. For example,ground pad 121 is attached to jack 115A labeled “G1” via cable 121A. Insome embodiments, the jacks G1, G2, G3, and G4 each provide a connectionto the generator reference potential. In one example, use of ground padsis relevant when the HF generator delivers an RF signal output toelectrode 150. In some embodiments, only one ground pad is used. In someembodiments, two or more ground pads are used. In some embodiments, thenumber of ground pads used is a function of the HF current expected tobe delivered by the ablation program selected by the user and themaximum current capacity of each ground pad under which skin burns canbe prevented. The HF generator 100 is adapted to measure the individualcurrent flow though each of the one or more ground pads 121, 122, 123,124 that are attached to the patient 190. In the embodiment shown inFIG. 1A, the current flowing through each ground pad is displayed to theuser by digital displays 103, wherein the individual current displays103A, 103B, 103C, 103D for the pads connected to jacks G1, G2, G3, andG4 are ordered from left to right on screen 101, in the same order as,and aligned with, their corresponding jacks G1, G2, G3, G4 for easyidentification by the user. In another example, the fraction I_(i)/I ofthe total current I that is flowing to each pad can be included indisplay 103, where I_(i) is the current flowing to pad i=1, 2, 3, 4 andI is the total current flowing from electrode 150; this can give a usera sense of the balance of current flowing to the pads and provideinformation for correcting improper ground pad adhesion to the skinand/or for rearranging the ground pads on the skin of the patient 190 toproduce a more balanced distribution of current among the pads. In someembodiments, the fractional of total current for each pad can beexpressed as a percentage of the total current I, or a percentage of thetotal current relative to a nominal percentage value, such as 100*1/Nwhich represents equal flow of current to each pad, where N is the totalnumber of ground pads, and N=4 in the example shown in FIG. 1A. Inanother example, the impedance between each ground pad and the ablationelectrode 150 can be included in display 103. Display 103 can providethe clinician user has an instant visual feeling if something is wrongwith a ground pad. For example, if a ground pad is losing contact withthe patient skin or is otherwise defective, then the current and/orimpedance related to that ground pad can change abnormally, and theclinician can be warned, thus avoiding possible skin burns. For example,if one ground pad is shielding current flow to another ground pad, suchas when one ground pad is placed distal to another ground pad on thelimb of the a patient 190, an abnormally low current can be displayed tothe user and the generator can warn the user about the suboptimal groundpad arrangement. In some embodiments, graphical display of theindividual ground pad currents, fractional currents, impedances, or somefunctions thereof can be including in display 103; the graphical displaycan be updated in real-time and can take the form of the one or more ofthe following: an analog meter, an indicator on a graduated scale, anindicator on a graduated dial, a bar graph, a bar chart, a graphicequalizer, a line graph over time, a plot of points (x,y) on x-axis andy-axis where x is a function of impedance and y is function of time, aplot as a function of a time axis, or another type of real-timegraphical display. A graph of the ground pad current that includes pastand present values, such as a line plot on a time axis, can show groundpad anomalies and trends that can indicate suboptimal or dangeroussituations to the clinician, and the chance of observation of an anomalyis increased since clinician can observe the signature of that anomalyin the graphical history at any time after the anomaly occurs, not justwhen the anomaly is occurring. For example, if one or more of the groundpads is lifting off the skin or is otherwise separated, then the graphicdisplay for that pad will show an anomaly, such as a dip in a currentgraph or a spike in an impedance graph. For example, if there isprogressive heating at the ground pad, the impedance graph can show atrend, such as a downward trend. One advantage of a graphic and/ornumerical display of a ground pad current and/or impedance is that itgives the clinician and instant warning of trouble with the equipment toavoid harm to the patient such as skin burns. Independently currentmonitoring of multiple ground pads by generator 100 provides theadvantage that very high levels of ablation current can be delivered toan ablation probe 150 or probes and distributed among multiple skinlocations on the patient 190, thus minimizing resistive heating currentat any one skin location and preventing ground pad skin burns.

In some embodiments, the generator 100 can include more than four groundpad jacks each with individual current monitoring. For example, thenumber of ground pad jacks can be a number selected from the list 1, 2,3, 4, 5, 6, 7, 8, 9 10, a number more than 10. One advantage of agenerator 100 including more than one ground pad jack is that highercurrents can be delivered to the ablation electrode or electrodes 150,particularly when multiple electrodes are energized at the same time.Another advantage of a generator 100 including more than one ground padjack is that smaller ground pads can be safely used with the generatorand skin burns can be prevented. One advantage of individual currentmonitoring of each ground pad is that imbalances in the currentdistribution, for example due to shielding of one ground pad by another,can be detected by the generator 100 and/or user, flagged to the user bythe generator 100, and the user can be prompted to reposition the groundpads to avoid skin burns.

In some embodiments, the generator 100 can include a switch between thereference potential and each ground pad jack G1, G2, G3, G4; a currentmeasurement for each ground pad jack G1, G2, G3, G4; and an automaticcontroller that varies the distribution of current among the ground padsconnected to the ground pad jacks in order to control the averagecurrent flowing to each pad. For example, by these mechanisms, thecurrent flowing through each pad can be equalized. For example, by thesemechanisms, the current flowing to each pad can be held below the upperlimit for each pad, above which a ground pad burn would be more likely.In one example, a repeating sequence of ground pad connections can beeffected automatically by the generator 100 wherein only one ground padis connected to generator potentials at a time; such a sequence can bereferred to as a sequential sequence. In another example, the generator100 can produce a repeating sequence of ground pad connections, whichcan be referred to as a “nested simultaneous” sequence, wherein eachsequence includes up to N+1 steps; wherein in the first step, all groundpads are connected to the generator reference potential; in eachsubsequent step, the highest-current pad that was active in the previousstep is disconnected from the reference potential; in the Nth step onlyone ground pad is connected to the reference potential; and in the(N+)-th step no ground pad is connected to the reference potential;wherein the duration of each step in each sequence is adjusted so thatthe root-mean-square (RMS) current for each pad over the duration of thesequence does not exceed an upper bound; and wherein N is the number ofground pads. In a more specific example, each sequence of the saidrepeating sequence only includes the steps subsequent to the i-th stepif the RMS current over the entire sequence would exceed the upper boundif those subsequent steps were not included, where i can take values 1,2, . . . , N. In another example, the generator 100 can reduce the totalHF current output so that the RMS current at each ground pad is lessthan the upper bound and the (N+1)th step can be excluded. One exampleof one sequence in a “nested simultaneous” sequence of ground padconnections can be G1, G2, G3, G4 connected for 0.5 second in step 1wherein G1 carries the most current; G1 disconnected and G2, G3, G4connected for 0.25 seconds in step 2 wherein G2 carries the mostcurrent; G1 and G2 disconnected and G3 and G4 connected for 0.1 secondsin step 3 wherein G3 carries the most current; G1, G2, and G3disconnected and G4 connected for 0.1 seconds in step 4; all ground padsdisconnected for 0.05 in step 5; wherein the RMS current of each groundpad is equal to the upper bound 900 milliamps RMS (mA-RMS); wherein RMScurrent is evaluated over the 1 second duration that includes steps 1through 5. One advantage of a nested simultaneous sequence of ground padconnections that controls the RMS current flowing to each pad is thatthe amount of ground pad switching can be reduced relative to asequentially switching sequence in which only one ground pad isconnected to the reference potential at any one time. One advantage of anested simultaneous sequence of ground pad connections that controls theRMS current flowing to each pad is that a higher total current can becarried by the ground pads than in a repeated switching pattern in whichonly one ground pad is connected to the generator 100 at the same time.

In some alternative embodiments, two or more of the ground pads 121,122, 123, 124 can be combined into a single skin-contacting padstructure such that each of the two or more ground pads make up some ofthe area of the said single skin-contacting pad structure and iselectrically isolated from the other of the two or more ground pads. Insome embodiments wherein two or more ground pads are combined into asingle skin-contacting pad structure, the said structure can have asingle cable that include a separate wire for connecting eachconstituent ground pad to the generator independently.

In some embodiments of generator 100, as shown in FIG. 1A, the electrodeoutput is regulated by its current value. The use of current-regulationfor the electrode output is an important for the use of a ground-padswitching process. For a regulated electrode current, tissue heatingnear in the electrode is invariant to the positive number of ground padsthat are connected and disconnected from the generator power supplyunless a limit of the power supply is reached, because even thoughchanges in the ground pad connections can affect the overall impedancebetween the electrode and the generator reference potential, the currentdensity (and therefore the power density and the rate of tissue heating)near the electrode is regulated. In contrast, in some embodiments, foran electrode output that is regulated by voltage or power, the voltagedrop and power loss in tissue near the electrode (which are responsiblefor tissue heating there) can change depending on magnitude of impedanceat points far from the electrode along the circuit path, because themagnitude of those distant impedances can affect the proportions of thetotal voltage drop and power loss (which is regulated) that occurs faraway from the electrode and near the electrode. Connecting anddisconnecting ground pads from the generator reference potential canaffect the impedance between the electrode and the reference potentialat locations that are distant from the electrode, thus affecting therate of heat near the electrode and the size of the ablation zone. Inone aspect the present invention relates to RF ablation system, such asgenerator 100, that includes controller that regulates the ablationelectrode current and changes the number of ground pads carrying currentfrom the ablation electrode.

FIG. 1A also shows an ultrasound machine 140 examining by means oftransducer 145 the patient body 190 and the particular region around thetarget organ 193 into which the electrode tip 151 is placed. Theultrasound imaging device 140 includes ultrasound controls 142 and RFgenerator controls 143. The ultrasound machine 140 is adapted to displaythe ultrasound image on ultrasound display 141. In one embodiment of theinvention, the ablation probe includes echogenic markings on its tip 151so that the tip portion is visually enhanced in the ultrasound display141 relative to the target organ 193 and any pathology in the organ suchas a tumor. In one example, the echogenic markings can compriseindentations in the surface of the probe tip portion 151 that areadapted to give enhanced ultrasound reflections. In some embodiments,the electrode shaft 152 can include echogenic markers that enhance shaftvisibility in ultrasound imaging of the shaft. In the example shown inFIG. 1A, the electrode shaft 152 is visible on the ultrasound display141 is the shaft of the ablation probe 150 and bubbles formed in thetissue around the tip 151. It is advantageous that the physician canmonitor and/or adjust the ablation process from the same console usingboth visual imaging, such as that from ultrasound imaging, and areal-time display of measured HF parameters, such as plotted time seriesof impedance and current. In some embodiments, the ultrasound image canbe displayed on the graphic display 101 or the generator 100; oneadvantage of this configuration is that the doctor can easily monitorand control the ablation process by imaging and generator readings atthe same time. In some embodiments, generator readings can be displayedon the graphic display 141 or the ultrasound machine 140; one advantageof this configuration is that the doctor can easily monitor and controlthe ablation process by imaging and generator readings at the same time.

FIG. 1A shows in a schematic drawing one example of a computer graphicdisplay 101 of the system 100. The graphic display 101 includes digitalreadings displays 104A, 104B, 104C, 104D, 104E, 104F of measuredparameters, including the electrode impedance 104A in units ohms (Ω),the electrode current 104B in units RMS Amps (A), the elapsed lesiontime 104C in minutes and seconds formatted MM:SS, the electrodetemperature 104D in units degrees Celcius (° C.), the electrode Voltage104E in units RMS Volts (V), and the electrode power 104F in units Watts(W). The graphic display 101 includes digital readings 103A, 103B, 103C,103D of measured current for each ground pad in units RMS milliamps(mA). The graphic display 101 includes a start/stop toggle button 105with which the user can turn the ablation output on and off. The graphicdisplay includes controls 106 for adjusting and displaying the settings106A, 106B, 106C, 106D, 106E and other controls, such as the “Main Menu”button 107, that provide for user-operated functions such as resettingthe ablation time (“Timer Reset”), saving a screen shot image of thescreen to generator memory (“Screen Shot”), printing a record of theprocedure to a printer if attached to a data jack 111 (“Print”), exportof procedure data to an external USB disk if connected to a data jack111 (“USB Export”), adding text notes to procedure data (“Notes”),transitioning to other screens and menus (“Main Menu”). The graphicdisplay 101 includes one or more line plots 102A, 102B, 102C of measuredparameters, including one or more of the parameters displayed digitallyas a function of time. The solid graph 102A can represent schematicallyone of the measured generator signal output parameters from the list ofpower, current, and voltage. The dashed-line graph 102B schematicallyrepresents the measured impedance of the ablation probe 150, forexample, in the case where an RF signal is applied between the electrodeactive tip 151 and one or more of the ground pads 121, 122, 123, 124,the measured impedance can be the impedance between the active tip 151and the energized ground pads 121, 122, 123, 124. The dotted graph 102Ccan schematically represent the temperature measured from the indwellingtemperature sensor is inside the ablation probe tip portion 151,essentially representing the temperature of the coolant inside the tipportion 151 of the ablation probe 150. The graphic display 101 and theline graphs 102A, 102B, 102C give the clinician a visual, intuitive, andreal-time update and evaluation of whether the ablation process isprogressing properly and safely. In one example, the graph 102A canrepresent signal output current. In one example, the graph 102A canrepresent signal output power. In one example, the graph 102A canrepresent signal output voltage. In one example, the graph 102A canrepresent the characteristic of the HF signal output that is beingautomatically regulated by the automatic control system of the generator100.

The dashed graph 102B represents schematically the output impedance. Theupward spikes, such as 118, represent the occurrence of substantialboiling and bubble formation in the tissue around the active and/orexposed tip 151 of the electrode 150. The bubble zone is the hottestregion and is located at a distance from the electrode tip 151 which iscooled. The presence of a bubble zone around the active tip 151represents an unstable situation. If the generator signal output is notreduced, a bubble zone will explosively expand, the impedance willrapidly increase, and the ablation current and ohmic heating power willbe reduced dramatically, for example, in the case of RF ablation. Thisunstable situation can be avoided or reversed by reduction of thegenerator HF signal output when the impedance spikes upward 118. Thegenerator 100 can be configured to automatically reduce the output levelwhen the impedance exceeds an upper limit, which can be set by the userphysician or by the factory, and which can be an absolute value or avalue relative to previously measured impedance values, such as a globalor local minimum among past impedance measurements during the presentablation routine. In one example, the upper limit can be 10 ohms abovethe minimum impedance during the present up time period. As shown inFIG. 1A, the HF output level signal 102A steps down from high values118A to much lower values 118B when the impedance signal 102B spikesupward. In one example, the signal output is reduced or modulated tonon-zero values 118B configured to allow for tissue cooling in the “downtime” (also referred to as “off time”) according to the control process.In another example, the signal output is reduced to zero for a “downtime” (also referred to as “off time” or “off period”) according to thecontrol process. The down time 118B allows the tissue to cool down andthe bubble zone to dissipate, as reflected by the impedance 102Breducing to a baseline value after spike 118. In some cases, theimpedance can continue to rise for a short duration after the beginningof a down time due to the response time of the controller or a lag inthe ablation process. After the down time, the ablation heating processcan resume with another “up time” (also referred to as “on time” or “onperiod”) by increasing the signal output to a higher level configured toheat tissue around the electrode active tip 151, such as the outputlevel immediately before the down time, or to a level somewhat below theoutput level immediately before the down time if, for example, theprevious up time was less than some lower bound indicating too muchoutput is being delivered to the tissue. During this up time, the signaloutput level can again heat the tissue and grow the bubble zone, so thatafter an up time duration, which depends on the signal output level andthe state of the tissue around the active tip 151, the impedance willonce again become unstable and spike upward, prompting the generator 100to initiate another down time cooling period with low output level. Therepeating process of up times and down times, one embodiment of which isshown by 102A and 102B, continues according to the control processprogrammed into generator 100. The repeating process of up times anddown times can maintain the impedance within a desired range. Inembodiments wherein a lower impedance-rise threshold is used, boilingcan be more limited, so a shorter down-time duration can be used, andthe repeating process of up times and down times can maintain theimpedance near to, at a desired level. In some embodiments, therepeating process of up times and down times can stabilize to a desiredlevel of signal output level during the up times, a desired duration ofup times, and a desired duration of down times to produce a desiredablation process and ablation size. In some embodiments, the controlsystem included in generator 100 uses the level of impedance spikes andthe signal output levels to stabilize the sequences of up times and downtimes so that the ablation process is uniform and reproducible for agiven electrode geometry and tissue impedance. The repeating alternationbetween up time 118A and down time 118B, the adjustment of the down timeduration, adjustment of the down time output level, and the adjustmentof the up time output level can proceed by automatic control by thegenerator 100. By multiple alternations of up and down time, andadjustment of the signal output level in response to parametersindicative of the ablation process, a high level of signal outputcurrent can heat tissue beyond high-impedance bubble zones and enlargethe ablation size. In some embodiments, tissue boiling can be detectedby a drop in current for a known or fixed applied voltage. In someembodiments, tissue boiling can be detected by a drop in power for aknown or fixed applied voltage.

The generator display 101 includes a numerical display of the durationof each up time and down time, such as 117A and 117B, each positioned onthe output level graph 102A near the location of its corresponding uptime or down time level. On display 101, numerical display 117A presentsthe time duration of up time 118A in seconds units as “109”, andnumerical display 117B presents the time duration of down time 118B inseconds units as “20”. The graph 102A includes four instances of uptimes and duration labels “109”, “40”, “9”, and “29” in seconds units,and three instances of down times and a duration labels “20”, “20”, and“22” in seconds units, wherein the duration label for each up time ordown time appears near its end point on the output level graph 102A. Insome embodiments, the up time and down time durations can be displayedin a different arrangement, such as a list. In some embodiments, otherparameters associated with an up time or a down time can be displayed,including for example, the average output level during an up time ordown time, the RMS current during an up time or down time, the RMSvoltage during an up time or down time, the average power level duringan up time or down time. Digital presentation of parameters related toeach up time and down time provide important information to the userphysician about the proper progress of the ablation progress. Thecombination of numerical and graphical presentation of parametersrelated to each up time and down time provide important information tothe user physician about the proper progression of the ablation process.

The generator 100 can include an automatic controller that uses one ormore measurement parameters as input for regulation of the output level,including for example the measured electrode impedance, current, power,voltage, and temperature. The generator 100 can include an automaticcontroller that includes one or more methods for regulating the outputlevel during the up times, including, for example, regulation of theoutput level as a function of the timing of impedance spikes in responseto variations in the output level, and regulation of the output level tocontrol the electrode temperature to a set point. In some embodiments,the generator 100 can include an automatic controller that includes bothsaid one or more methods for regulating the output level during the uptimes, and a method of alternating up time and down time in response toimpedance spikes. For example, for embodiments in which the indwellingtemperature sensor of the electrode 150 is positioned in the coolantflow and therefore effectively measures the coolant temperature, theoutput level during the up times can be regulated to fix a parameter ofthe output level, such as current, voltage or power, and alternation ofup time and down time in response to impedance spikes can be the primarymeans of feedback control of the output level in response to unmeasuredtemperature changes in the tissue. In another example, for embodimentsin which the temperature measurement more directly measures the maximumtissue temperature (for example, in the case where the cooled electrodeincludes an temperature-sensing extension tip that extends distal orlateral to the active tip 151, or in the case where an separate remotetemperature probe is positioned near the electrode active tip 151), theoutput level can be regulated to hold the measured temperature at ornear a set value, and the alternation of up time and down time inresponse to impedance spikes can be used to dissipate bubble zones thatcan form either because the temperature set value is intentionally setto produce tissue boiling, or because inaccuracies in the temperaturemeasurement lead to undesired tissue boiling even though the temperatureset value is set to a value expected to prevent tissue boiling.

The solid graph line 102A represents the HF output level delivered tothe electrode. The graph 102A shows a sequence of plateaus and stepswhich can represent a sequence in which the generator 100 automaticallyregulates the output level to hold the output level at or near asequence of set levels for a parameter of the output signal, such as thecurrent, power, or voltage. For example, the output level graph 102Awithin up time 118A can reflect the output set level stepping from aninitial value of 2.3 Amps, to 2.4 Amps after 30 seconds, and then to 2.5Amps after another 30 seconds; and after this, within the down time118B, the output level graph 102A can represent the output level beingregulated at or near a level of 100 mA. For each instance of up time,the output level increases in steps of 100 mA after each 30 seconds ofelapsed up-time duration. One advantage of slowly increasing the outputlevel while ablation energy is being delivered to the tissue is that theduration of the up time as an indication of the tissue's ability tocarry more tissue-heating current without boiling rapidly and therebyinterrupting tissue heating. For each instance of up time, the initialoutput level of the up time is 100 mA less than the final output levelof the previous instance of up time if the total duration of theprevious up time is less than 10 seconds or if the duration of the finaloutput-level step of the previous up time is less than 10 seconds;otherwise, the initial output level for each instance of up time isequal to the final output level of the last instance of up time. In someembodiments, a threshold duration other than 10 seconds (eg a valueselected form the range 0-30 seconds or more) can be used in relation tothe final output-level step of the previous up time to determine whetherthe next up time starts at the same level or a lower level than theprevious up time ended. One advantage of decreasing the initial outputlevel of the next up time when the previous up time's duration is tooshort is that a short up time duration is an indication of the tissue'sinability to carry the output level of previous up time without rapidlyboiling, and thereby interrupting heating. The duration of the initialdown time is 20 seconds. The duration of subsequent instances of downtime are increased by 2 seconds relative to the duration of the previousinstance of down time when the total duration of the prior instance ofup time is less than 10 seconds. In some embodiments, a thresholdduration other than 10 seconds (eg a value selected form the range 0-30seconds or more) can be used in relation to the duration of the previousup time to determine whether the down time duration is increased. Oneadvantage of increasing the duration of the down time as function of theup time duration is that a short up time can indicate that a longercooling time is required before the next up time in order to morecompletely dissipate the bubble zone to allow for continued tissueheating. One advantage of increasing the duration of the down time asthe total elapsed lesion time increases is that total lesion time iscorrelated with larger lesion size, larger bubble zone size, and thus alonger required duration of cooling for complete bubble zone dissipationbetween up times to allow for continued tissue heating. One advantage ofincreasing and decreasing the output level in response to the durationof up time, when the duration of the up time is influenced by increasesin the measured impedance indicative of tissue boiling around the activetip 151, is that, even without direct tissue temperature measurements,the output level can be adjusted to tissue conditions around the activetip, which conditions can vary in an unpredictable manner as a functionof tissue type, blood flow, tumor type, disease state, tissueinhomogeneity, patient variability, and other factors. One advantage ofincreasing and decreasing the output level in response to the durationof up time, when the duration of the up time is influenced by increasesin the measured impedance that are indicative of tissue boiling aroundthe active tip 151, is that the output level can be increased to a higha level as possible to increase lesion size, while preventingexcessively rapid heating that can hinder the progression of heat lesionsize, for instance due to irreversible changes such as tissue charring,or rapid boiling. In some embodiments, the parameters of the up time anddown time pulsing process can be adjustable or selectable by the user,wherein the parameters can include the impedance threshold forterminating an up time, the duration of the downtime, the rate ofincrease of the output level during an up time, the up time durationbelow which the output level of the next up time is reduced, the up timeduration below which the duration of the subsequent down time isincreased, other parameters described herein, and other parameters.

Settings panel 106 presents one example of user settable parameters(“settings”) that influence the behavior of the ablation controllerincluded in generator 100 to suit clinician user needs. The settingsinclude a set time 106A, an initial current 106B, a maximum current106E, a set temperature 106C, and a mode 106D setting, which in FIG. 1Atake values 9:00 minutes, 2.3 Amps, 80 deg C., and “automatic”,respectively. The set time 106A determines the amount of time anablation program will be run before the generator 100 automaticallyshuts it off, and in some embodiments, it can take values in the range0-30 minutes or more, in one-second increments. The total duration ofthe ablation process has an effect on ablation size, and properselection of the total duration of an ablation process is an importantfactor for producing reproducible and predicable heat lesions. In someother embodiments, the stopping criteria for the ablation process can bethat a one or more of the quantifies in the following list exceeds athreshold value: total ablation program running time (ie set time 106A),total duration of up time, time-integrated power, time-integratedsquared RMS current, total energy deposition into the tissue, thebaseline impedance value, a temperature measured at a distance from theactive tip 151, an indication of tissue heating within some volume, animaging parameter. The initial current setting 106B, displayed in unitsAmps (A) which is equal to 1000 milliamps (mA), determines the targetthe output level for the beginning of the first “up time”, and in someembodiments, it can takes values between 0-3000 mA (RMS) or more, in 1mA or 10 mA increments. In FIG. 1A, after the output is turned on and aninitial coolant test period 118C, the output level 102A is rapidlyramped to this level, and then the output level is increased anddecreased in response to measured impedance to maximize the output levelcurrent without excessively, sub-optimally heating the tissue. In someembodiments, it is advantageous to select a starting output level thatis likely to be below the minimum maximal output level for the electrodetip size 151 and the target anatomy 193 conditions in order to preventan initial overheating of the tissue that could limit the ultimatelesion size, and to allow for calibration of the output level to thetissue conditions which cannot be precisely predicted. In someembodiments, it is desirable to allow the user to set a maximum outputlevel, such as a maximum current, voltage, or power, to preventoverheating of the tissue. The maximum current setting 106E, displayedin units Amps (A) which is equal to 1000 milliamps (mA), determines themaximum target output level for all “up time” during the ablationprogram. The setting 106E allows the user to limit the maximum outputlevel during an “up time”, for example, to prevent too rapid heatingwhich can limit lesion size, or to provide for additional safety in casewhere is there a problem with feedback control of the “up time” outputlevel. In some embodiments, the maximum current 106E can takes valuesbetween 0-3000 mA (RMS) or more, in 1 mA or 10 mA increments. The settemperature 106C determines the measured temperature value that thegenerator 100 will try to achieve by regulation of the output level,unless the output level is limited by another control objective, such asthat of the initial current or that of impedance control. In someembodiments, the set temperature can take values in the range 0-100 degC. or more, in 1 deg C. increments. Regulation of the measuredtemperature can be important to prevent excessive tissue heating in thecase of coolant flow failure. Regulation of the measured temperature canbe important when a temperature measured remote of the active tip 151 isused to regulate lesion progression. The mode setting 106D allows theuser to select among automatic output control using the otheruser-selectable parameters (setting value “Auto”), and manual outputcontrol by means of the manual control knob 110, which can be apotentiometer, a rotary encoder, an encoder, an on-screen slider, oranother device for selecting a value, such as quantized or real values,within a range of valves (setting value “Manual”). It is advantageous toallow for both automatic and manual control of the output level so thatthe clinician user can select automatic control when an automaticimplementation of the control process can outperform a human controller,and can select manual control when the ablation is not proceeding in amanner consistent with programmed processes. In some embodiments, themode setting 106D can provide additional settings to the user, such asimpedance control, fixed current control, fixed power control, fixedvoltage control, manual control with an automatic temperature limit,manual control with an automatic output level limit. In someembodiments, the generator 100 can regulate the voltage in steps, andthe initial voltage can be in the range 0-200 V-RMS or more, in 1 Vincrements. In some embodiments, the generator 100 can regulate thepower in steps, and the initial power can be in the range 0-400 W ormore, in 1 W increments.

In the embodiment presented in FIG. 1A, all settings shown in settingspanel 106 can be active at the same time. This embodiment allows theuser to select cooled-probe non-temperature control by turning on thecoolant pump (for example by means on control 133 or an on-screen 101button) when using a cooled electrode 150 for which the temperaturesensor is absent or immersed in intra-probe coolant, and selectnon-cooled-probe temperature control by turning off the coolant pump forthe same probe. One advantage of this configuration is the ability torapidly switch from cooled RF ablation mode to non-cooled trackcoagulation mode after a cooled-RF heat lesion is generated in a tumorand the physician desired to coagulate the needle track of the cooled-RFprobe. Another advantage of the setting configuration presented in 106,is that the same settings can be used both for an internally-cooledprobe whose temperature sensor is positioned within the coolant flow,and for an internally-cooled probe whose temperature sensory ispositioned at a distance from the coolant flow (such as the extensiontip electrode 160 in FIG. 1B), since both a temperature setting and acurrent setting are active at the same time. Another advantage of thesetting configuration 106 is that if either temperature or impedancefeedback is not functioning properly, the other feedback setting canstill provide control and safety.

A very important and useful advantage for the clinician user is to havean instant and intuitively clear visual check and feedback on thestability and control of the ablation process as it proceeds,particularly for impedance-controlled pulsing processes, of which oneembodiment is presented in FIG. 1A. This intuitive visual feedback isprovided, in one example, by a computer-graphic real time display of thegenerator signal output 102A during the procedure. This intuitive visualfeedback is provided, in one example, by a computer-graphic real timedisplay of the generator signal output 102A and impedance 102B duringthe procedure. This intuitive visual feedback is provided, in oneexample, by a computer-graphic real time display of the generator signaloutput 102A, impedance 102B, and temperature 102C during the procedure.For embodiments in which the displayed output level parameter is powerand/or current, the up times and down times and the stability of thepower and/or current level can visually indicate the clinician at aglance if the ablation process is going stably according to theautomatic process, or if the ablation process is suboptimal, forexample, the tissue is being overheated locally and instances of boilingare occurring too rapidly (as indicated by impedance rises in responseto the output level) to optimally heat tissue beyond a high-impedancebubble zone. One example of a scenario in which a graphical display canprovide information about a suboptimal ablation process involves theup-time power and/or current being too high, leading to excessiveboiling around the active tip 151, the rapid and/or sustained formationof a high-impedance bubble zone, and a slump, a decrease, erraticvariations, or other otherwise unstable variations displayed is the linegraph of output current and/or power 102A. In another example scenariowherein the displayed output parameter is voltage, excessive voltagelevels during the up time periods can cause the tissue to boil andimpedance to be elevated in a sustained and/or frequent manner thatprevents growth in lesions size and can lead to erratic controllerbehavior which can be detected by the user as erroneous by observationof the line plot of the voltage over time. Another example of a scenarioin which graphical plot of the generator output level over time can helpthe user clinician troubleshoot a problematic ablation process is whereincorrect output levels, output settings that are inappropriate for theablation probe and tissue conditions, controller malfunction, and/orcontroller mismatch to tissue conditions produce incorrect, erratic, orunstable variations in the graphical plot of the generator signal outputlevel and/or the up times and downtimes observable in that graphicalplot. In another example, the graphs can show that the output level istoo low; this can be indicated by the absence of an impedance spikeafter a sustained delivery of an output level, such as a constantvoltage, constant current, or constant power. A too low output level canoccur due to initial selection of the output level at a too low valuefor the probe size and tissue conditions. A too low output level canoccur due to a too large reduction in the output level after animpedance spike; therefore, monitoring of a too low output level can beimportant throughout an ablation process. These and other examplescenarios can be visualized and instantly and intuitively accessed bythe clinician by the graphic real time display of one or more of thesignal output parameters in the list of power, current, and voltage.These and other example scenarios can be visualized and instantly andintuitively accessed by the clinician by the graphic real time displayof impedance and one or more of the signal output parameters in the listof power, current, and voltage, in real time, on the same axis. Thisgives the advantage of safety and control.

In other embodiments, two or more of the parameters impedance, voltage,current, and power can be plotted on the same time axis, in real time,for an ablation electrode output; this can provide the similarinformation to plotting impedance and one or more of voltage, current,and power, in real time on the same time axis. For example, for acontrol process in which a constant voltage is delivered, a drop in thecurrent or the power can indicate a boiling condition. This instantvisual feedback to the user is adventurous for the user to monitor thestability and efficacy of a pulsing ablation process by means of aninternally-cooled HF probe, such as a cooled RF electrode, wherein thetissue repeated produces tissue boiling. This instant visual feedback isalso important for non-cooled HF ablation processes to detect undesiredboiling conditions.

In other embodiments, only a signal output level parameter, such asvoltage, current, and power is plotted in real time. For example, ifcurrent and/or power is the sole plotted parameter, a drop in theplotted parameter can indicate a boiling condition that has producedsuch high impedance that the HF electrical supply is not able to deliverthe desired plotted level. This does not provide as sensitive and rapidan indication of the ablation process as plotting two or more of theparameters voltage, current, power, and impedance on the same time axisin real time. Though this does not provide as rich information as thetime-registered plotting of two or more of the parameters voltage,current, power, and impedance, it can provide some information about theablation process, particularly for cooled HF ablation processes thatintentionally produce tissue boiling, in accordance with aspects of thepresent invention.

In some embodiments, the control system measures the impedance betweenthe electrode 150 and ground pads 121, 122, 123, 124. In someembodiments, the control system measures the level and timing of upwardimpedance spikes, as well as the level and timing of the post-spikedecrease and stabilization of the impedance, and the control system usesthat information to adjust the ablation process as it progresses, suchas adjusting the timing and/or durations of the up-time phases anddown-times phases, and/or the levels of the signal output during thesephases. In some embodiments, the impedance is not displayed on thecomputer graphic display, but the processing of the impedanceinformation is done within the control system according to itsprogramming, and the results of the processing is indirectly manifest inthe graphic display of the one or more signal output parameters, such as102A. In some other embodiments, including that presented in FIG. 1A,the impedance is displayed on a computer graphic display, eg 102B, andthis display can be an important for the clinical user to assess theefficiency, effectiveness, and safety of the ablation process. Forexample, graphical plotting of the impedance 102B can demonstrateirregularity, erraticness, and non-smoothness indicative of unstablelesion formation and improper placement of the probe. In someembodiments, the simultaneous graphical display of impedance 102B andthe signal output level 102A provides the clinical user with animmediate sense of the progress of the ablation process, the correctnessor incorrectness of the ablation control process relative to the tissueconditions, the tissue reaction to the applied HF output, and therelative timing and amplitude of impedance spikes relative to outputlevel variations such up times and down times. The graphic displays ofimpedance 102B and the one or more output parameters 102A can be stackedon each other, overlaid relative to the same time scale, or presented onthe same two instances of the same time axis, either on the samecomputer graphic display 101 or on multiple displays. One advantage ofgraphical displays 102A and 102B is that the clinician can user them tovisually evaluate the relation of impedance behavior and behavior of theone or more signal output parameters to see if the control system isfunctioning properly.

In some embodiments, a temperature is measured by the generator 100,such as the temperature of a temperature sensor integrated into theelectrode 150E, and thus into the assembly probe 150, when the electrode150E is inserted into cannula 150U. In some cases, the temperaturesignal can be measured by the generator 100 and used as an input to theablation control process, but not displayed graphically to the user, forexample, on screen 101. In some other embodiments, the electrodetemperature can be displayed graphically, as shown for example by lineplot 102C in FIG. 1A, on the same time axis as the output level graph102A and the impedance graph 102B. One advantage of displaying thetemperature graphically 102C in sync with the output level 102A, is thatthe temperature response of the electrode 150, the coolant flowingthrough the electrode, and/or the tissue near the electrode active tip151 can be intuitively assessed by the user during the ablation process.For example, when the temperature sensor of electrode 150 is in thecoolant flow path, variations in the temperature graph indicates to theuser the effectiveness of the electrode cooling. For example, if thetemperature were to rise substantially during the up times of theablation process, the user would be prompted to evaluate the coolantflow rate and check for any flow blockages, electrode malfunction, orelectrode misconstruction. In the example shown in FIG. 1A, graph 102Cshows moderate increases in temperature during the up times due to thecoolant being heated by elevated tissue temperatures around the activetip 151, and decreases temperature during the downtimes due todissipation of temperature in the tissue around the active tip 151.

One general advantage of a graphical display of the output level 102A,the impedance 102B, and/or the temperature 102C that displays thehistory of one or more of these values during the ablation process isthat the user can observe variations in these values over time, and hasaccess to a documentation of past irregularities that might otherwise bemissed if the user does not happen to look at a digital display 104A,104B, 104C, 104D, 104E, 104F of an irregular value at the moment theirregularity occurs; this is particularly important for automatedprocesses that alternate between states, such as up times and downtimes, since the operating conditions of the generator 100 and ablationprocess can change discontinuously and/or rapidly. Another advantage ofdynamics graphs of the output level 102A, the impedance 102B, and/or thetemperature 102C over time is that the clinician can use it to performan instant check on the proper operation of the control system andablation process over the entirety of the preceding duration of theablation process.

In some embodiments, the signal output level, such as the level graphedby line plot 102A, can be displayed as voltage, current, power, RMSvoltage, RMS current, RMS power, duty cycle, duty cycle of a set outputlevel, time-averaged voltage, time-averaged current, time-averagedpower, RMS voltage over a time window, RMS current over a time window,RMS power over a time window, or mathematical functions of these values,where a mathematical function can be, for example, addition,subtraction, multiplication, an average, an average over a time window,the root mean squared value over a time window, squaring, cubing, squareroot, logarithm, and combinations of these mathematical functions.

In some embodiments of the system shown in FIG. 1A, one of the usersettings “initial current” 106B or “maximum current” 106E (which are oneexample of settings that control the output level of the beginning ofthe initial pulse, and the maximum output level of all pulses,respectively, in a cooled-RF system and method for impedance-basedpulsed control of the ablation process) can be omitted. For example, inFIG. 1B and FIG. 1C, only one current setting is available to the user.In some embodiments wherein one of the user settings “initial current”106B or “maximum current” 106E is omitted, the value of the omittedsetting can be automatically determined by the control system relativethe value of the remaining displayed user setting. For example, if theuser selects 1900 mA for the “initial current” setting 106B and setting106E is not available for user selection, the controller canautomatically set a control variable for the “maximum current” to besome amount higher than the “initial current” user setting value 106B,such 2500 mA, a difference of 600 mA. Similarly, for example, if theuser selects 2300 mA for the “maximum current” setting 106E and setting106B is not available for user selection, the controller canautomatically set a control variable for the “initial current” to besome amount lower than the “maximum current” user setting value 106E,such 1800 mA. The controller can set the relative value for a maximumcurrent or an initial current setting relative a user-selected value forinitial current or maximum current, respectively, by adding orsubtracting a predetermined value from the user-selected value (such asa value in the range 100 mA to 800 mA, 600 mA, a value less than 100 mA,a value greater than 800 mA), by multiplying the user-selected value bya fraction (such as a value in the range 0.8-1.2, a values less than0.8, a value greater than 1.2), or another method for selecting relativevalues to suit clinical needs. In some embodiments wherein the maximumcurrent is not user-settable, the maximum current can be set to themaximum current output level for the generator. In some embodiments, theinitial output level and the maximum output level can be parameterizedby voltage, power, current, or another measurement of output level. Insome embodiments, a minimum output level (such as a current level) canbe included as a user setting.

Referring now to FIG. 1B, FIG. 1B is a schematic drawing showing oneexample of an arrangement of an apparatus for performing HF ablation ofbodily tissue of patient 190, in accordance with some aspects of thepresent invention. In some embodiments, the apparatus of FIG. 1B can beanother configuration of the apparatus of FIG. 1A, wherein electrode 150is replaced by electrode 160 and the generator settings 106 takedifferent values. Electrode 160 includes an extension tip 167 thathouses a temperature sensor configured to monitor tissue temperaturedistal to the active tip 161 of the electrode 160, close to or at thelocation of maximum tissue temperature. The generator settings 106include a set temperature value of 95° C. The combination of theextension tip 167 temperature sensor and the set temperature areconfigured to hold the maximum tissue temperature just below the boilingpoint in order to maximize heat lesion size and to prevent tissueboiling. The generator control system is adapted to measure the extendedtemperature from sensor 167, and to display the extended temperature119C on the computer graphic display 101 together with other signaloutput parameters in the list of power, current 199A, voltage, andimpedance 119B. The control system is can be adapted to use the extendedtemperature 167 as a feedback parameter in the ablation process. In oneexample, the extended temperature can be a check that the boiling bubblezone, or potential boiling bubble zone, is in the desired range oftemperature and time duration. By displaying the extended temperature119C along with the other output parameters 119A and 119B, the cliniciancan have visual check and confirmation of the ablation process.

Electrode 160 is connected to generator electrode jack 116 via cable 164that carries HF output to the electrode 160. Coolant, such as chilledsaline or water, is pumped through tube 165 into the electrode 160,flows through the electrode shaft to cool the active tip 161, and outfrom the electrode through tube 166 and into collection container 135.Electrode 160 includes a hub 163 at the electrode proximal end, anelongated shaft including an insulated portion 162 at the shaft proximalend and a conductive active tip 161 at the shaft distal end, anextension tip 167 extending distal to the distal end of the active tip161, wherein the extension tip 167 includes a temperature sensor at adistance from distal end of the active tip 161, wherein the distancebetween the extension tip temperature sensor 167 and the distal end ofactive tip 161 can be a value in the range 0.1 mm to 10 mm (or valueadapted to locate the temperature sensor at the most likely location ofmaximum tissue temperature), wherein the insulated portion 162 preventsoutflow of the generator's HF output signal, and wherein active tip 161allows outflow of the generator's HF output signal to the bodily tissueof organ 193 of body 190 and thereby generates heat lesion 194B. In someembodiments, the temperature sensor can be at the distal end of theextension tip 167. In some embodiments, electrode 160 is introduced intobodily tissue by means of an introducer cannula that can betissue-piercing or that can be configured to be tissue-piercing by meansof a sharp-point stylet. In some embodiments, the introducer cannula canhave sharp bevel at its distal, and a removable stylet with match-grounddistal bevel, to reduce insertion forces when the cannula is insertedinto patient tissue 190. In some embodiments, the distal extension tip167 can be electrically uninsulated so that it does produces HF heatingof the tissue by itself, and measures the temperature of the tissue at adistance D from the end of the active tip 161. In some embodiments, thedistal extension tip 167 can be electrically insulated so that theextension tip 167 does not produce HF heating of the tissue by itself,and thus less influences the temperature of the tissue at a distance Dfrom the end of the active tip. The distance D can be predetermined sothat sensor is located in the hottest part of the tissue duringablation. Alternatively, the distance D can be adjustable by the user ifthe extension tip is configured to slide relative to the active tip 161.In some embodiments, the extension tip can be slidably mounted to theactive tip 161, perhaps via other elements of the electrode 160, such asa clamp in the electrode hub 163, so that the user can measuretemperature at multiple locations distal to the tip 161 by sliding theextension tip 167 relative to the active tip 161. In some embodiments,the extension tip can be fixedly mounted to the active tip 161. In someembodiments, the distal extension tip 167 can comprise a stainless steeltube, a temperature sensor at the distal point of the tube (for example,formed by welding a constantan wire within the stainless steel tube tothe distal end of the stainless steel tube), electrical insulation(which can comprise a plastic coating or sheath along the tube, and gluecovering wire connections at the tube proximal end) covering all but thedistal point of the tube; wherein the tube proximal end is positionedwithin an inner lumen of the electrode shaft 162 and tip 161 (forexample, the lumen can be formed by a pipe within the shaft 162 and tip161 that is welded to the distal end of the pipe that forms the outersurface of the tip 161, between both of which pipes, the coolant fluidflows and is contained), the tube position is fixed relative to theactive tip 161 by a thermally-insulative element at a proximal locationwithin the electrode 160 (for example, by glue within the electrode hub163), and the extension tip 167 is thereby thermally, electrically, andphysically separated from both the active tip 161 and the coolant flowwithin the electrode shaft 162 and tip 161, both by a physical gap (iethe space between inner surface of the lumen and the outer surface ofthe tube electrical insulation) and the electrical insulation coveringthe tube; and wherein the wires connecting to the extension tiptemperature sensor to the generator 100 are electrically isolated fromthe HF output wires in the electrode 160, cables 164, and generator 100;so that the extension tip 167 does itself produce HF heating of thetissue, and the extension tip 167 measures temperature of the tissue ata distance D from the end of the active tip 161 with a fast thermalresponse due to the metallic temperature sensor that is integral withthe outer surface of the distal end of the extension tip 167 and that isin direct contact with bodily tissue 190. In some embodiments, thedistal extension tip 167 can comprise a stainless steel tube, atemperature sensor at the distal point of the tube (for example, formedby welding a constantan wire within the stainless steel tube to thedistal end of the stainless steel tube), electrical insulation (whichcan comprise a plastic coating or sheath along the tube, and gluecovering wire connections at the tube proximal end) entirely coveringall parts of the extension tip 167 that emerge from the tip 161 and thusdirectly contact tissue 190; wherein the tube proximal end is positionedwithin an inner lumen of the electrode shaft 162 and tip 161 (forexample, the lumen can be formed a pipe within the shaft 162 and tip 161that is welded to the distal end of the pipe forming the outer surfaceof the tip 161, between both of which pipes, coolant fluid flows and iscontained), the tube position is fixed relative to the active tip 161 bya thermally-insulative element at more proximal location in theelectrode 160 (for example, by glue within the electrode hub 163), andthe extension tip 167 is thereby thermally and physically separated fromboth the active tip 161 and the coolant flow within the electrode shaft162 and tip 161, both by a physical gap (ie the space between innersurface of the lumen and the outer surface of the tube electricalinsulation) and the electrical insulation covering the tube; and whereintube can either be electrically insulated or not electrically insulatedwithin the electrode 160 and cable 164 from the HF output delivered tothe active tip 161 by generator 100; so that the extension tip 167 doesitself produce HF heating of the tissue because its outer surface iselectrically insulated, and the extension tip 167 measures temperatureof the tissue distance D from the end of the active tip 161.

In the example presented in FIG. 1B settings panel 106 includes a settime of 12 minutes, a set current of 3 Amps, a set temperature of 95°C., and manual control mode. In some embodiments, these settings cantake values in the ranges described in relation to FIG. 1A. In someembodiments, the set temperature for an electrode 160 with atemperature-sensing extension tip, it is advantageous to select a settemperature sufficiently below boiling to avoid boiling across anexpected variety of typical tissue conditions. For example, the settemperature can be in the range 40-90 deg C., 40 deg C., 50 deg C., 60deg C., 70 deg C., 80 deg C., 45 deg C., 55 deg C., 65 deg C., 75 degC., 85 deg C., or 90 deg C. The HF current output delivered to electrode160 is plotted over time by solid line 119A. The electrode impedance isplotted by dashed line 119B on the same time axis. The electrodetemperature, measured by the temperature sensor included in theextension tip 167, is plotted by dotted line 119C on the same time axis.The graphed values 119A, 119B, 119C were generated by the followingprocess that involved both manual and automatic control functions. Afterthe user started with ablation program, since the control mode is set to“Manual”, the user increased the HF output current by turning thecontrol knob 110 counter clockwise to a sufficient level to heat thetissue around the active tip 161. Before the output level reached thecurrent limit of 3.0 Amps, the generator automatically adjusted theoutput level 119A to ramp the measured temperature 119C up to the settemperature value 95° C. over approximately 2 minutes. A slow ramp up tothe set temperature, for example wherein the ramp to full temperatureoccurs over 1 to 3 minutes, has the advantage of preventing tissueboiling due to a lag in the measured temperature response, particularlyfor large active tips 161. Once the temperature 119C reaches the settemperature value, the generator 100 controller automatically adjuststhe HF output level 119A to maintain the measured temperature 119C atthe set temperature setting value. During the heating process, theimpedance 119B first decreases in value as the tissue around the activetip 161 heats up, and then rises slowly and smoothly as irreversibletissue changes occur and micro bubbles form around the active tip 161.In another embodiment, the control mode can be set to “Auto” with theother settings 106 taking the same values as shown in FIG. 1B, andtemperature-controlled ablation can proceed without user interaction viathe control knob 110. One advantage of a generator 100 that can controlan ablation process by measurement of tissue temperature remote of theactive tip 161, such as by means of an extension tip 167 or side-outlettemperature sensor, is that tissue heating can be sustained withoutinterruptions and/or “down times” (as in FIG. 1A). In some embodiments,the temperature control configuration presented in FIG. 1B can producesubstantial tissue boiling and impedance spikes, such as 118 in FIG. 1A.In that case, if the control mode of generator 100 is set to “Auto”, thegenerator can use the impedance-controlled up-time/down-time pulsingprocess presented in FIG. 1A in coordination with thetemperature-control process presented in FIG. 1B, wherein the outputlevel during the up time is modulated to maintain the measuredtemperature at or near the set temperature setting value. One advantageof a controller that includes both a temperature-control controller andan impedance-based pulsing controller is that direct temperaturemeasures can be used to control the ablation process, and output pulsingcan be used to dissipate high-impedance bubble zones that can form whentemperature control fails, for example, because the temperature sensoris not located at the exact location of maximum tissue temperature orbecause the temperature-control controller's programming is not wellmatched to particular tissue conditions.

Referring to FIG. 1C, FIG. 1C is a schematic drawing showing one exampleof an arrangement of an apparatus for performing HF ablation of bodilytissue of patient 190, in accordance with some aspects of the presentinvention. In some embodiments, the apparatus of FIG. 1C can be anotherconfiguration of the apparatus of FIG. 1A, wherein electrode 150 isreplaced by three ablation electrodes 150A, 150B, 150C arranged incluster, and the generator settings 106 take different values. In theembodiment shown in FIG. 1C, each of the ablation probes 150A, 150B, and150C are integral tissue-piercing RF electrodes. Electrodes 150A, 150B,150C are connected to HF output jack 116 by splitter cable 154A whichcarries HF output to each electrode. In the embodiment shown in FIG. 1C,the same HF output signal is applied to all electrodes 150A, 150B, 150C,each of which include a temperature sensor that is positioned withinthat electrode's active tip. Return current from the electrodes 150A,150B, 150C are carried by ground pads 121, 122, 123, 124. This can bereferred to as a “monopolar cluster” configuration. The inflow andoutflow tubes of the electrodes 150A, 150B, 150C are connected inseries, and coolant is pumped through tube 155A into electrode 150A; outfrom electrode 150A, through tube 155B, and into electrode 150B; outfrom electrode 150B, through tube 155C, and into electrode 150C; and outfrom electrode 150C, through tube 155D, and into the waste container135. The electrodes are held in a triangular arrangement by guideblock157, wherein the electrode shafts are substantially parallel and theelectrodes are equidistant from each other. The guideblock 157 can be asolid block (or another type of rigid structure) that includes holesthrough which, or slots into which, the electrodes shafts can slide. Theguideblock 157 can include multiple sets of holes to allow for differentparallel electrode spacings, such as 5 mm, 10 mm, 15 mm, 20 mm, 25 mm,and 30 mm. In some embodiments, the block 157 can be one of theguideblocks presented in relation to FIG. 25, 26, 27, 28. One advantageof heating tissue with a cluster of closely-spaced electrodes is that alarger heat lesion zone 194C can be generated, for instance, to destroya large tumor in a large organ 193 such as the liver, lung, or kidney.Another advantage of the a guideblock 157 is that two or more electrodesinserted into the same body 190 can mechanically support each other toprevent movement due to electrode weight outside the body 190. Anotheradvantage of a guideblock 157 is that two or more lesions can be createdsequentially to produce a total lesion zone of an irregular shape. Insome embodiments, the guideblock can allow for unequal parallelelectrode spacings, such as three electrodes with inter-electrodespacings 10 mm, 15 mm, and 15 mm. In some embodiments, wherein thenumber of electrodes is 4, a square or quadrangular parallel-electrodeguideblock can be used. In some embodiments, a guideblock canaccommodate two or more electrode arranged in an arbitraryparallel-shaft configuration. In some embodiments, a guideblock canprovide for surrounding one of more electrode by three or moreelectrodes, wherein all electrodes are parallel. In some embodiments aguideblock can provide for non-parallel electrode arrangements. In someembodiments, a non-parallel-electrode guideblock can be configured toprovide for avoidance of sensitive or impenetrable bodily structureslike the rib that can prevent some parallel-electrode configurations. Insome embodiments, a guideblock can provide for the non-parallelplacement of multiple electrode active tips are location within the bodyin an arrangement that is configured to produce a uniform ablationvolume around the multiple active tips. In some embodiments, guideblock157 can have guide holes whose inner diameter is large relative toelectrodes 150A, 150B, and 150C so that the electrodes are inserted bythe physician in a non-predetermined configuration, and the physiciancan adjust the relative position and alignment of electrodes to adapt toanatomical constraints.

The settings panel 106 shows that the set time is set to 12:00 minutes,the initial current to 2.4 Amps, the set temperature to 90 deg C., andcontrol mode set to Automatic. Because the temperature sensors ofelectrodes 150A, 150B, 150C are positioned within the coolant flowwithin the electrode active tips, the output level is not limited by therequirement of hold the measured temperatures at or below 90 deg C., andthe generator operates in an pulsing impedance-control mode, analogousto that of FIG. 1A. Correspondingly, the output level goes throughmultiple cycles of high-output up times and low-output down times asshown by current graph 102D; the impedance goes through multiple cyclesof spikes and returns to baseline as shown by impedance graph 102E; andthe electrode temperatures 102F, 102G, 102H rise and fall moderatelyduring up times and down times, respectively.

Referring to FIG. 1C, the graphic display 101 shows four digitaltemperature readings 104G labeled “T1”, “T2”, “T3”, and “T4”, whichreplace the single digital temperature reading 104D shown in FIG. 1A.The generator 100 automatically changes the digital and graphicaltemperature-reading displays when the number of temperature readingsdetected on the pins of 116 changes, reflecting a change in the numberof temperature-sensing electrodes 150A, 150B, 150C attached to jack 116by splitter cable 154A. The splitter cable 154A can include markers bywhich the user can match an electrode 150A, 150B, 150C to a temperaturereading label “T1”, “T2”, “T3”, and “T4”. In the example shown in FIG.1C, temperature readings T1, T2, T3 come from electrodes 150A, 150B,150C, respectively. In some embodiments, the number of temperaturereadings can be equal to the number of detected temperatures. In someembodiments, changes in the number of displayed temperature readings canbe prompted by one or more of the list: user selection of settingsvalues, jumper pins in adaptor cable 154A, circuitry in adaptor cable154A, circuitry in each electrode 150A, 150B, 150C, and othermechanisms. The fourth temperature display 104H, labeled “T4” indicatesthe absence of a fourth temperature reading by means of the “--”indicator. In some embodiments, a fourth electrode analogous toelectrode 150A can be attached to jack 116 with a four-electrodesplitter cable. The display screen 101 includes graphical display of thegenerator output level as solid line 102D, the impedance between thegenerator reference potential and HF output as dashed line 102E, thetemperature of electrode 150A as dotted line 102G labeled “T1”, thetemperature of electrode 150B as dotted line 102H labeled “T2”, and thetemperature of electrode 150A as dotted line 102F labeled “T3”. Labels“T1”, “T2” 102I, “T3” appear on the screen next to the right end oftemperature graphs 102G, 102H, 102F to identify the graphs to the user.Label 102I reads “T2” and labels line 102H.

Paragraph B: The impedance 104A and 102E, current 102D, voltage, andpower displays pertain to the HF current flowing between the electrodes150A, 150B, 150C and ground pads 121, 122, 123, 124 that are attached togenerator potentials, where the electrodes 150A, 150B, 150C can beconnected and disconnected from the HF output potential, and the groundpads 121, 122, 123, 124 can be connected and disconnected from thereference potential. In the example presented in FIG. 1C, the electrodes150A, 150B, 150C are uniformly connected to the HF output signal, andthe ground pads 121, 122, 123, 124 are connected to the referencepotential in a repeating switching pattern configured to maintain theRMS current of each ground pad below at maximum of 700 mA, which is themaximum safe current rating for each pad, in this example. Generally,ground pad heating is influenced by the RMS current averaged over timewindows that are short relative to the thermal response time constant ofthe ground pad, for example time windows up to 5-10 seconds, or up to 30seconds, or longer for some ground pads. For a HF signal, such as a 500kHz RF signal, the RMS current over a time window W with duration |W|much longer the HF signal's carrier is the square root of the integralof I²(t) with respect to time t over time window W, where I(t) is theRMS Current over the period of the carrier of the HF signal; that is((1/|W|)*∫_(W) I²(t)*dt)^(1/2). For a 500 kHz RF signal, the carrier canbe a sinusoidal signal with period 2 microseconds. In the example shownin FIG. 1C, for the total electrode current 2500 mA=2.5 A, theindividual ground pad currents 700 mA, 699 mA, 659 mA, 576 mA for padsG1 121, G2 122, G3 123, G4 124, respectively, can be achieved to withinsingle-digit precision by a first pattern of switched ground padconnections, which can be classified as a “nested simultaneous”switching pattern. In the first step of the first pattern, jacks G1, G2,G3, G4 are connected to the generator reference potential for 4.35seconds, and return current flows to the jacks' respective pads inproportions 0.3, 0.28, 0.22, 0.2, respectively. In the second step ofthe pattern, jacks G2, G3, G4 are connected to the generator referencepotential for 0.31 seconds, and return current flows to the jacks'respective pads in proportions 0.4, 0.33, 0.27, respectively. In thethird step of the pattern, jacks G3, G4 are connected to the generatorreference potential for 0.34 seconds, and return current flows to thejacks' respective pads in proportions 0.55, 0.45, respectively. Theduration of the pattern is 5 seconds. The RMS current for jack/pad G1over the pattern duration can be computedsqrt((4.35/5)*(2500*0.3)̂2)=699.55 mA. The RMS current for jack/pad G2over the pattern duration can be computedsqrt((4.35/5)*(2500*0.28)̂2+(0.31/5)*(2500*0.4)̂2)=698.78 mA. The RMScurrent for jack/pad G3 over the pattern duration can be computedsqrt((4.35/5)*(2500*0.22)̂2+(0.31/5)*(2500*0.33)̂2+(0.34/5)*(2500*0.55)̂2)=658.74mA. The RMS current for jack/pad G4 over the pattern duration can becomputedsqrt((4.35/5)*(2500*0.2)̂2+(0.31/5)*(2500*0.27)̂2+(0.34/5)*(2500*0.45)̂2)=576.03mA. One advantage of this first example of a “nested simultaneous”switching pattern for four ground pads is that only three switchingsteps are used to maintain the ground pad currents at or below theirmaximum rating. One advantage of reducing the number of ground padswitching steps is that it can increases the maximum power that thegenerator can deliver to the electrode by reducing switching transitiontimes, it can reduce wear and tear on the ground pad switches, it canreduce switching noise, and it can reduce impedance variations due tochanges in the ground pad connection configuration. One advantage ofmaximizing the number of active ground pads in a switching pattern isthat the peak current to any one pad is minimized since the totalcurrent is distributed across a maximum number of pads. The precisionwith which the ground pad currents can be controlled can be limited bythe maximum switching speed, the minimum possible duration of a step ina switching pattern, the speed with which the total electrode currentcan be adjusted, and other factors. In another example, a secondnested-simultaneous switching pattern can be used to equalize theRMS-average ground pad currents, so that each ground pad carries 682mA+/−2 mA over the sequence of ground-pad connection states in thepattern. In this second pattern, the total current 2500 mA and theproportion of current flow to each pad is the same as in the first threesteps of the first pattern described above, and a fourth step is addedin which only jack G4 is connected to the generator reference potentialand all the return current flows to the G4's pad 124. The durations ofsteps 1 through 4 of the second pattern are 4.15 seconds, 0.3 seconds,0.46 seconds, and 0.09 seconds, respectively. The total time of thepattern is 5 seconds. The RMS current for jack/pad G1 can be computedsqrt((4.15/5)*(2500*0.3)̂2)=683.28 mA. The RMS current for jack/pad G2over the pattern duration can be computedsqrt((4.15/5)*(2500*0.28)̂2+(0.30/5)*(2500*0.4)̂2)=683.15 mA. The RMScurrent for jack/pad G3 over the pattern duration can be computedsqrt((4.15/5)*(2500*0.22)̂2+(0.30/5)*(2500*0.33)̂2+(0.46/5)*(2500*0.55)̂2)=682.53mA. The RMS current for jack/pad G4 over the pattern duration can becomputedsqrt((4.15/5)*(2500*0.2)̂2+(0.30/5)*(2500*0.27)̂2+(0.46/5)*(2500*0.45)̂2+(0.09/5)*(2500*1.00)̂2)=681.01mA. One advantage of the second example of a nested-simultaneousswitching is pattern is that current is evenly distributed across theground pads on average. One advantage of both the first and secondexamples of a nested-simultaneous switching is pattern is that the RMScurrent for each ground pad over the duration of the switching patterncan be less than that produced by a sequential switching pattern whereinonly one ground pad is active at a time. For example, for a totalcurrent flow of 2500 mA and a sequential switching pattern in which eachof four pads/jacks G1, G2, G3, G4 is connected to the generatorreference potential for 1.25 seconds with all other pads disconnected,the RMS current over the total 5 second pattern issqrt((1.25/5)*(2500*1.0)̂2)=1250 mA. In the preceding examples, switchingground pad connections between subsequent pattern steps is assumed to beinstantaneous. In practice, in some embodiments, non-zero switching timecan be used. When non-zero switching time is used, the total switchingpattern duration can be increased to include the switching time and/orthe step durations can be reduced to remove the switching time. In someembodiments, the HF output is disabled during the time when a ground-padswitch is opening or closing. This produces a non-zero switching time,and it advantageously avoids high-current arcing within the switches andthe production of non-zero-mean transients in the electrical signal.Because switching can take up to several milliseconds, and becauseground pads can carry high currents from an ablation electrode,non-zero-mean signal transients can produce undesired nerve-stimulationeffects on the patient in some cases. In the prior art of Lee, it issuggested this can be avoid by timing ground pad switches withzero-crossing of the RF. One limitation of this approach is thathundreds of zero crossings will occur during even one millisecond ofswitch transition time (eg a 500,000 Hz RF signal has period of 0.002milliseconds). Another limitation is that the switching signal must besynchronized with accuracy on the order of one microsecond. In Lee, itis suggested that stimulation of excitable tissue can be avoid duringground pad switching by the application of a high-pass filter. Onelimitation of this approach is that for the very high output levelscharacteristic of tissue ablation, a high pass filter may not reducestimulating transients to below a level capable of stimulation. In oneaspect of the present invention, a RF ablation generator turns off theRF output during changes to the state of ground pad switches. This hasthe advantage of completely removing stimulating transients due toground pad switching. This has the advantage of enabling the use ofhigher ablation output levels both by switching ground pad connectionsto limit ground pad heating, and by avoiding simulative effects ofground pad switching.

In some embodiments, the electrodes 150A, 150B, 150C are connected tothe pump 130 in a parallel configuration. This has the advantage allelectrodes received coolant at the same temperature. This contrasts aserial coolant flow configuration, such as that shown in FIG. 1C,wherein a downstream electrode, eg 150B, is cooled by coolant that issomewhat heated after having already flowed through one or upstreamelectrodes, eg 150A. One advantage of a serial configuration issimplicity of setup since a single pump tube can be used to carry waterto and from the cluster of multiple electrodes 150A, 150B, 150C.

In some embodiments, the cluster electrodes 150A, 150B, 150C can beinserted into the tissue without the use of a guideblock. In someembodiments, cluster electrodes can be inserted in a non-parallelconfiguration and an ellipsoidal or pseudo-ellipsoidal lesion zone canform around the cluster of non-parallel active tip as long as the tipsare sufficiently close, for example 5-15 mm apart, because thermalconduction tends to smooth irregularities and/or non-convexities in theheating pattern around the active tips. In some embodiments, guideblock157 provides electrode holes and/or slots that allow for non-equidistantspacing of multiple electrodes; this has the advantage of allowing theinsertion of electrodes around bony structures such as the ribs thatmight block an equidistant electrode configuration, while at the sametime constraining the active tips of the electrodes to be in a knowngeometrical configuration, such as a parallel-shaft isosceles-triangleconfiguration, a parallel-shaft arbitrary triangular configuration, aparallel-shaft quadrangular configuration, a non-parallel shafttriangular or quadrangular configuration in which the active tips willbe in non-parallel but sufficiently close proximity to create a convexheat lesion when inserted to a predetermined depth beyond theguideblock, and other configurations.

In some embodiments, a different HF output signal is conducted to eachcluster electrode 150A, 150B, 150C, wherein the HF output signals candiffer, for example, in their amplitudes or in their patterns ofconnection and disconnection from generator output potentials.

In some embodiments, the generator 100 only measures the temperature ofone of the clustered electrodes 150A, 150B, 150C. In some embodiments,each of the electrode 150A, 150B, and 150C can include extension tips,like that of ablation electrode 160 in FIG. 1B, and the generator canmaintain all electrode temperatures below the set temperature value, forexample, by adjusting the output level to maintain the maximum of allelectrode temperatures at or below the set temperature value.

In some embodiments, the one or more ablation probes 150, 150A, 150B,150C, 160 are non-internally-cooled probes, such as a non-cooled MWantenna, a standard non-cooled RF electrode, or a non-cooled RFelectrode inserted into an RF cannula. In some embodiments, thegenerator 100 can be configured for nerve ablation, for example forfunctional neurosurgical procedure and/or for pain managementprocedures. In some embodiments, the generator 100 can include a nervestimulator. In some embodiments, ablation probes 150, 150A, 150B, 150C,160 are perfusion electrodes from which fluid is pumped into the tissuearound the active tip to enhance heat lesions size. In some embodiments,a cooled RF electrode also includes outlets in or near its active tipconfigured for perfusion of fluid into the tissue; the perfused fluidcan include some of the cooling fluid, or the perfusion fluid can beanother fluid, or both. In some embodiments, a perfusion RF electrodecan output into the tissue all the cooling fluid supplied to it by apump. In some embodiments, a perfusion RF electrode can output into thetissue a portion of the cooling fluid supplied to it by pump, and cancirculate back up the shaft and into a output tube another portion ofthe cooling fluid supplied to it by the pump. In some embodiments,ablation probes 150, 150A, 150B, 150C, 160, can each be any one ore thefollowing: cooled RF electrode, a cooled RF electrode inside an RFcannula, cooled RF electrode with extension-tip temperature sensor,cooled RF electrode with lateral temperature sensor, cooled RF electrodetemperature sensory on outer surface proximal to the active tip,perfusion RF electrode, cool-wet RF electrode, single-prong cooled RFelectrode, multi-prong cooled RF electrode, cooled cluster RF electrode,a cooled RF cluster electrode with two electrode shafts, a cooled RFcluster electrode with three electrode shafts, a cooled RF clusterelectrode with four electrode shafts, a cooled RF cluster electrode morethan four electrode shafts, multiple RF electrodes of any of theaforementioned types, cooled MW ablation antenna, multiple cooled MWablation antennae, a cluster MW antenna, and other type of HF ablationprobes. In some embodiments, a cluster RF electrode can have a number ofshafts selected from the list: 2, 3, 4, 5, 6, 7, 8, 9, 10, more than 10.

The present invention, as shown in one embodiment in FIG. 1, has theadvantages of producing reproducible and predicable size of ablationzone, and presenting measurements to the user to maintain efficacy andsafety during HF heat ablation. The visual graphic display of output (egcurrent, voltage, or power) and tissue parameters (eg impedance) duringthe ablation process allows the user to correlate clinical outcomes,both positive and negative, with behaviors displayed by the displayedparameters, so that the user can improve his or her ability to interpretthe parameters and adjust the ablation setup in future cases. This is aparticularly significant advantage in the case of HF ablation using aninternally-cooled electrode 150 (which, in one example, can be cooled RFablation), because the ablation process involves repeatedly approachingunstable boiling tissue conditions. To bring stability to this unstableprocess and to enable visual conformation is a significant advantage.Another advantage of the embodiment presented in FIG. 1 is the abilityfor the same generator 100 to operate in a variety of configurations tosuit clinical needs, wherein the configurations differ in the types andnumber of ablation probes, types of parameters controlled, and theparameter values of automated ablation controllers.

Referring now to FIG. 2, one embodiment of a multi-electrode ablationsystem is presented in a schematic drawing in accordance with severalaspects of the present invention. Many elements of the system in FIG. 2are analogous to elements of the system presented in FIG. 1, and thesystem in FIG. 2 presents additional functionality including performingtissue ablation on multiple electrodes at the same time with independentmeasurements, digital displays of measurements, graphical displays ofmeasurements, and settings; and energizing multiple electrodes andground pads at the same time or in arbitrary sequences of connection todifferent generator potentials such that current flows betweenelectrodes and either other electrodes or ground pads either at the sametime or at different times. Generator 200 is configured as an RFgenerator as shown in FIG. 2, and in other configurations and similarembodiments can be a MW generator, a hybrid RF and MW generator, oranother kind of HF generator for tissue ablation. Generator 200 isconnected to four ground pads 221, 222, 223, 224 placed on the skinsurface of patient 290; four internally-cooled treatment electrodes 251,252, 253, 254 that are placed in the bodily tissue of patient 290;coolant pump 230 that includes two pump heads 231, 231A; and ultrasoundimaging machine 240 by means of which the internal anatomy of patient290 can be visualized. Ground pads 221, 222, 223, 224 are connected togenerator jacks 215 labeled “G1”, “G2”, “G3”, “G4”, respectively. Groundpad 221 is connected to jack G1 by cable 221A. Ablation electrodes 251,252, 253, 254 are connected to generator electrode jacks 216 labeled“E1”, “E2”, “E3”, “E4”, respectively. Electrode 251 is connected to jackE1 by cable 251A. Ultrasound imaging machine 240 includes ultrasoundtransducer 245 which can display images of the internal anatomy ofpatient 290 and electrodes 251, 252, 253, 254 within that anatomy ondisplay 241; controls 242; and generator controls 243 by means of whicha user can operate the generator 200 via data connection 244. Coolantpump 230 includes user control 233 and two pump heads 231, 231Aconnected to coolant reservoirs 232, 232A, respectively, wherein thecoolant can be a fluid such as sterile water or sterile saline solution.Pump head 231 pumps coolant from reservoir 232 through tube 251B intoelectrode 251 to cool the electrode's active tip, and then out throughtube 252B into electrode 252 to cool that electrode's active tip, andthen out through tube 252C into collection container 235. Pump head 231Apumps coolant from reservoir 232A through tube 254B into electrode 254to cool the electrode's active tip, and then out through tube 253B intoelectrode 253 to cool that electrode's active tip, and then out throughtube 253C into collection container 235. One advantage of thisconfiguration is that two fluid pump heads can cool four cooled ablationprobes. Generator 200 includes touch screen 201; ultrasound machinecontrols 213 by means of which the user can control ultrasound machine240 via data connection 244; four ground pad jacks 215; four ablationprobe jacks 216; a control knob 210; a button 209 to disable and/ordiscontinue delivery of ablation energy to the electrodes; a button 208to enable delivery of ablation energy to one or more electrode jacks 216and electrodes attached to those jacks; a lamp 214 indicating activedelivery of ablation energy to jack 216; data ports 211 which canprovide for export of data, printing of data, input of data, input ofcontrol signals from remote controllers, and other data input andoutput. The touch screen 201 includes a toggle button 205 for activatingand deactivating delivery of ablation energy to attached electrodes 251,252, 253, 254; a settings panel 206 for display and user-adjustment ofgenerator settings such as the set time, set current, set temperature,and other parameters of ablation programs included in generator 200; andcontrol buttons 207 for selecting cooled RF ablation mode, selectingstandard RF (aka coagulation) lesioning mode, selecting pulsed RF lesionmode of the variety familiar to one skilled in the art of spinal nerveablation and pain treatment, selecting nerve stimulation mode, resettingthe lesion program timer, saving an image of the screen to memory,entering procedure notes to stored procedure data, printing storedprocedure data, exporting stored procedure data to an external disk, andchanging the screen display to main menu screen. In some embodiments,including other operating modes of generator 200, settings panel 206 canallow the user to select different settings for each electrode E1, E2,E3, E4. In some embodiments, the settings in panel 206 can take valuesin the ranges described in relation to settings 106A, 106B, 106C, 106D,106E. The display screen 201 includes display 203 which displays anindividual current for each ground pad attached to ground pad jacks G1,G2, G3, and G4. All ground pad jacks, and their attached ground pads,can be connected to the generator reference potential at the same time,or can be connected and disconnected from the generator referencepotential to limit, equalize, or otherwise control the average currentflow through each pad. The display 201 includes an individual modeselection button 217, individual set of digital displays 204, andindividual graphical displays 202A, 202B for each electrode jack E1, E2,E3, E4 and each electrode 251, 252, 253, 254 attached to those jacks,respectively. The mode-selection control 217 for electrode jack E1 andelectrode 251 provides controls, for example by means of a drop-downmenu, for activating and deactivating jack E1, selectingelectrode-specific settings for electrode 251, and selecting the patternof connections between jack E1 and generator output potentials. Control217 displays “E1 Bi->2” indicating that the control and displays belowit correspond to the electrode attached to jack E1 and that electrode E1and electrode E2 are energized in a bipolar (also known as “dual”)configuration, wherein current flows between electrodes E1 and E2. Thecontrol display for electrode E2 reads “E2 Bi->1” also indicating abipolar configuration between electrode jacks E2 and E1. The control forelectrode E3 reads “E3 Mono” indicating that electrode E3 is energizedin a monopolar configuration wherein return currents from electrode E3are carried by one or more of the ground pad jacks. The control forelectrode E4 reads “E4 Mono” indicating that electrode jack E4 isenergized in monopolar configuration. In another embodiment, the control217 for electrode E1 can read “E1 Cluster->E2,E3” indicating thatelectrodes E1, E2, E3 are connected to the same HF output signal andenergized as a monopolar cluster, referenced to one or more ground pads.

In some embodiments, groups of electrodes are energizednon-concurrently, so that only one group is connected to and energizedby a generator power supply at any one time, and groups are energizedrepeatedly and sequentially; for example, for the case depicted in FIG.2, the generator can first drives RF current between E1 and E2 with E3,E4, and ground pads disconnected; then drive RF current between E3 andone or more ground pads with E1, E2, and E4 disconnected; then drive RFcurrent between E4 and one or more ground pads with E1, E2, and E3disconnected; and then continue sequentially delivering RF signal outputto each of the groups bipolar pair E1-E2, monopolar output E3, andmonopolar output E4. For a generator setting configuration wherein E1and E2 are energized in a “cluster” configuration, in one step of anon-concurrent activation sequence, the generator connects E1 and E2 tothe same electrical potential and current flows from both E1 and E2 toone or more ground pads, with E3 and E4 disconnected. In someembodiments, one electrode can appear in more than one group. Oneadvantage of a non-concurrent activation sequence is that currents donot flow between electrodes of different groups and the pattern of RFcurrent flow and heating patterns between electrodes can be controlled.

In some other embodiments, electrode groups are activated at the sametime. This has the advantage of simplicity, and RF heating patterns arenot affected if electrodes in different groups are spaced far enoughaway from each other.

In some other embodiments, electrodes in different groups are connectedto different, isolated RF power supplies. This had the advantage of notrequiring temporal sequencing of electrode group activation.

Digital displays 204 present measurements specific to electrode E1 251:temperature, impedance, lesion time, voltage, current, and power (fromtop to bottom). A similar set of digital displays is included on display201 for each other electrode jacks, organized and ordered from left toright in the same organization and order as jacks E1, E2, E3, and E4.Underneath the controls and digital displays for electrodes E1 and E2 isa plot 202A of measured readings as a function of the lesion time foroutputs E1 and E2. Graphical plot 202A is labeled “E1 E2” and includes asingle solid line for the current, a single dashed line for impedance, adotted line for the temperature of electrode E1, and a dash-dot line forthe temperature for electrode E2. Since electrodes E1 and E2 areenergized in a bipolar configuration, the HF current flowing throughjack E1 is the same as the current flowing through jack E2, and thus asingle current measurement for both is sufficient information about theoutput level for both electrodes. Similarly, there is only one impedancebetween jacks E1 and E2 since there is only one voltage applied betweenthe jacks and only one current flows between the jacks. Graph 202A showsthat an impedance-controlled pulsing process, similar to that presentedin FIG. 1A, is applied to electrodes E1 and E2 by generator 200. Thisconfiguration generates a bipolar heat lesion 294A connecting andsurrounding the active tips of electrodes 251 and 252 within organ 293A.Below the control for electrode E3 labeled “E3 Mono” are digitaldisplays of temperature, impedance, lesion time, voltage, current, andpower for electrode 253, and a time graph 202B of current (solid line),impedance (dashed line), and temperature (dotted line) for electrode253, which indicates that generator 200 is using an impedance-controlledpulsing process to control the monopolar ablation zone 294C around theactive tip of electrode 253 within organ 293C. Electrode 4 has analogousdigital and graphical displays monitoring its ablation progressdisplayed under its control labeled “E4 Mono”. Electrode E4 254 ispositioned at a different location within the same organ 293C aselectrode E3 253 is positioned in order to target two spatially-separatetargets, such as two tumors. In the example shown in FIG. 2, the useractivated bipolar output E1-E2, monopolar output E3, and monopolaroutput E4 at different times using their respective output controls 217,and thus the elapsed lesion times for outputs E1-E2, E3, and E4 aredifferent. Features presented in FIG. 1, such as display of up and downtimes, ground pad switching and control, multiple operating and controlmodes, and other features, can be combined with the embodimentspresented in FIG. 2. One advantage of the ablation system presented inFIG. 2 is that multiple ablation probes can be independently energized,monitored, and controlled by the same generator 200. The generator 200includes graphical displays of multiple ablation processes 202A, 202B;this display is important for monitoring multiple ablation processesbecause the history of each ablation process, including anomalies, canbe assessed rapidly by the user physician, even when that assessmentoccurs after an anomaly of other important event occurs. In someembodiments of the system presented in FIG. 2, the number of ground padscan be one or more. In some embodiments, the number of ground pads canbe a number selected from the list: 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, anumber greater than 10. In some embodiments of the system presented inFIG. 2, the number of electrode can be two or more. In some embodiments,the number of electrodes can be a number selected from the list: 1, 2,3, 4, 5, 6, 7, 8, 9, 10, a number greater than 10. In some embodiments,each of the treatment electrodes 251, 252, 253, 254 can be any one ofthe following: non-cooled RF electrode, non-cooled RF electrode in an RFcannula, cooled RF electrode, a cooled RF electrode inside an RFcannula, a cooled RF electrode with extension-tip temperature sensor,cooled RF electrode with lateral temperature sensor, cooled RF electrodetemperature sensory on outer surface proximal to the active tip,perfusion RF electrode, cool-wet RF electrode, single-prong cooled RFelectrode, multi-prong cooled RF electrode, cooled cluster RF electrode,a cooled RF cluster electrode with two electrode shafts, a cooled RFcluster electrode with three electrode shafts, a cooled RF clusterelectrode with four electrode shafts, a cooled RF cluster electrode morethan four electrode shafts, multiple RF electrodes of any of theaforementioned types, non-cooled MW antenna, cooled MW ablation antenna,multiple cooled MW ablation antennae, a cluster MW antenna, and othertype of HF ablation probes.

Referring to FIG. 3, one example of a graphic display of measured RFablation parameters during one example of a HF ablation using a cooledRF system and control method in accordance with several aspects thepresent invention. In some embodiments, the graphs shown in FIG. 3 canbe generated and displayed by the systems presented in FIG. 1A, FIG. 1C,FIG. 2, FIG. 6, FIG. 7, FIG. 8, FIG. 9, and FIG. 10. For example, theplots shown in FIG. 3 can be a specific example of graph 202B on screen201 in FIG. 2 with the addition of a power graph 340.

In one example, the graphs in FIG. 3 can be measurements from tissueablation using an electrode system in which a 17-gauge cooled RFelectrode inserted into a 15-gauge RF cannula with 5 cm active tip atits distal end, wherein the electrode distal end aligned with thecannula distal. The cannula active tip is energized by the electrode andis positioned percutaneously within a large tumor in the patient'sotherwise healthy liver, wherein the tumor is a colorectal metastasiswhose width is 4.5 cm to 5.5 cm. The electrode temperature sensor ispositioned near the electrode distal end, within the internal coolantflow path. The electrode is cooled by chilled saline. The electrode isenergized by the RF generator in a monopolar configuration whereinreturn currents are carried by by four large-area ground pads placed onthe anterior and posterior aspects of both thighs of the patient. Theresulting lesion volume is 5 cm to 6 cm in width and completely coversand destroys the tumor in a predictable and stable manner by means ofaspects of the present invention.

The computer graphic display in FIG. 3 includes line graphs of theelectrode current 300 in units milliAmps (mA), electrode impedance 350in units Ohms (Ω), electrode temperature 330 in units of degreesCentigrade (° C.), and electrode power 340 in units Watts (W). Thevertical scale for current and power is shown on the left, and thevertical scale for impedance and temperature is shown on the right side.The temperature graph 330 monitors the temperature of the coolantflowing inside the electrode active tip and provides an indication thatthe cooling process and coolant system are functioning properly. All theline graphs 300, 350, 330, 340 are stacked, overlapped, and registeredto the same time scale 390, and can be easily visually compared.

In the example presented in FIG. 3, the control system ramps up thecurrent 300 step-wise, increasing 100 milliAmpere (mA) every 30 seconds,starting from 2000 mA, which is conservatively below the equilibriumoutput level for the electrode and tissue. By 2400 mA in phase 305, theimpedance begins to spike upward 352. The automatic control systemtriggers on impedance spikes and reduces the current for the down-timeduration that is determined by the automatic controller, such as inphase 306. The automatic controller times the down time according,raises the signal output current to a level to start an up time phase(such as step 307), and possibly adjusts the high output current furtheruntil the next impedance spike, at which point the automatic controllerreduces the current substantially for the next down time. The process ofsequences of up times and down times continues for the duration of theablation process. The automatic controller and control system areadapted to adjust the level of generator signal output current and theduration of up times and down times so that the sequence settles to astable process. In the example shown in FIG. 3, the current levelstabilizes to about 2400 mA during the on times, and the durations ofthe on times and off times settle stabilize at about 20 seconds each.The clinician user can select the total duration of the ablation programbased on the control-method type, the of the generator signal outputcurrent, the chosen electrode active tip size, the size of the targetstructure, and the size of the desired ablation zone. In the exampleshown in FIG. 3, the clinician can know from clinical experience thatabout 12 minutes is sufficient time to cover and destroy the targettumor, given the control-method type, output current level, andelectrode type.

In the example presented in FIG. 3, the controller regulates the outputcurrent. In another example, the controller regulates power. In anotherexample, the controller regulates voltage. In one example, thecontroller regulates the ablation process by monitoring the impedanceand uses that to control the modulation of at least one of the outputparameters in the list of power, current, and voltage. The example ofFIG. 3 illustrates how the present invention enables a stable,controlled, and reproducible ablation process that has real time visualconfirmation.

The following description of the FIG. 3 includes several examples ofablation processes, steps, and branch points that can produce the graphspresented in FIG. 3. The generator begins the ablation process at timezero (0) on time axis 390. The generator quickly ramps 301 the outputlevel at a rate of 100 mA/sec, up to the initial current level 2000 mA,which is conservatively below the equilibrium current value for theknown electrode type, geometry, and size, and for the known conditionsof the tissue around electrode active tip. During the initial ramp 301,the power 340 increases to approximately 200 W, the impedance 350 beginsto drop as tissue adjacent to the electrode active tip heats up, and themeasured temperature increases moderately by 5-10 deg C. as heat isconducted from heated tissue into the coolant. After ramp 301, thegenerator increments the set current by a step of 100 mA after every 30seconds of elapsed time. The set current goes from 2000 mA in step 302,to 2100 mA in step 303, to 2200 mA in step 304, to 2300 mA in step 305.Correspondingly, the power goes from 200 W to 330 W. The step increment100 mA and the step time 30 seconds are controller parameters configuredto slowly increase the output level to determine a maximal, stableoutput level for the ablation process. Phases 302, 303, 304, and 305 arecollectively the first “up time” of the ablation. The generatorcontroller executes this schedule of current steps in all up timeslonger than 30 seconds, for example up time 307, 308; and up time 310,311. One advantage of adjusting the up-time output level in steps isthat sufficient time elapses after each adjustment of the output levelfor the system to respond to that level, and if the response isunfavorable, the change can be reversed or moderated by a step decrement(described below). In some embodiments, the step size can be a value inthe range 0-200 mA or more. In some embodiments, the elapsed up-timebefore a step increase can be a value in the range 0-120 sec or longer.In some embodiments, the up-time output level can be increased in acontinuous, smooth, linear, concave-up, or concave-down ramp, and theramp rate can be in the range 0-10 mA/sec. In some embodiments, the ramprate can be configured to allow for discrimination of the maximumablation current level that the tissue can carry without boiling toorapidly. In some embodiments the up-time output level can be increase ina ramp after a delay, wherein the delay can be a value in the range0-120 sec or longer.

The first up time is terminated in phase 305 when the impedance 350spikes upward, rising more than 20 Ohms above its minimum value 351 fromthe initial ramp phase 301 and the first up time. The impedance-increasethreshold of 20 Ohms is one example of a criteria for detecting boilingin the tissue around the electrode active tip. This criteria forterminating an up time based on impedance spike is applied throughoutthe ablation process in FIG. 3. In some examples, the impedancethreshold for up-time termination can be in the range 0-50 ohms. In someexamples, the impedance threshold for up-time termination can be greaterthan 50 ohms. In some examples, the impedance threshold for up-timetermination can be an absolute impedance value. In some examples, theimpedance threshold for up-time termination be A*Zmin, where Zmin is theminimum impedance from the last up time, and A is a number greater than100%, such as 105%, 110%, 115%, 120%, or another number.

After step 305, the generator controller decreases the output to a lowlevel 306 configured to allow for tissue cooling and the dissipation ofthe bubbles around the electrode active tip. This is the first down time306 of the ablation session. During this down time, the current isapproximately 100 mA and the power is approximately 0.5 Watts. Thegenerator controller initializes the down-Ill time duration at 20seconds, and increments the down-time duration by 2 seconds whenever thepreceding up-time duration is less than 10 seconds to allow for morecooling time in subsequent down times. The initial down-time duration 20seconds is configured to provide for sufficient cooling after impedancespikes in the initial phase of tissue heating. The down-time increment 2seconds is configured to allow for more cooling time as the lesion sizegrows. The minimum up-time duration 10 second is a threshold configuredto identify whether insufficient cooling occurred during the precedingdown time. In the example of FIG. 3, the duration of initial down time306 is 20 seconds because the preceding up time 302, 303, 304, 305 isgreater than 20 seconds. Similarly, every down time before down time 315has duration 20 seconds because all up times until up time 314 arelonger than 10 seconds. Because up time 314 is shorter than 10 seconds,the subsequent down times 315. Because up time 316 exceeds 10 seconds,down time 317 also lasts 22 seconds. Because up time 318 is shorter than10 seconds, the subsequent down times 319 lasts 24 seconds. Because uptime 320 exceeds 10 seconds, down tune 321 also lasts 24 seconds.

In the example presented in FIG. 3, the generator determines thestarting set current for an up-time based on the duration of the finalset-current step in the previous up-time. If that duration is at least10 seconds, the up-time starts with the same set current as the end ofthe previous up-time, as illustrated by steps 305 and 307 wherein step305 has duration greater than 10 seconds, and wherein both step 305 and307 have set current 2300 mA. However, if that duration is less than 10seconds, the up-time starts with a set current that is 100 mA less thanthe set current at the end of the previous up-time, as illustrated bysteps 311 and 313, wherein step 311 has duration less than 10 seconds,and wherein the set current of step 311 and 313 differ by 100 mA. Steps314 and 316 are another example of a set current decrement, wherein step314 has duration less than 10 seconds, the subsequent up time 316 has aset current 100 mA less than that of step 314. The minimum step time 10seconds is a duration configured to identify whether an output level canbe used to heat tissue stably without too-rapid boiling. The stepdecrement 100A is a value configured to reduce the generator output whentissue boiling occurs too rapidly, and thus to determine a stable outputlevel for the ablation process.

In the example presented in FIG. 3, the generator controller adjusts theoutput level, up time durations, and down time durations to achievestable values for tissue ablation. For example, for every up-timebetween the including 313 and 314, the up-time set current is 2400 mA,the up-time durations are between 10 and 30 seconds, the down-time setcurrents are 100 mA, and the down-time durations are 20 seconds. Theachievement of stable, maximal ablation parameters provides for a highdegree of tissue heating without producing high-impedance boiling toofrequently, which might otherwise hinder lesion size growth.

For the example in FIG. 3, the set time is 12:00 minutes, so theablation program is automatically discontinued by the generator at 720seconds. This lesion time can be configured by the user to produce amaximal and reproducible lesion size. The total time of the ablationprogram can be determined as a function of the electrode geometry,electrode type, electrode tip length, tissue type, disease type, targetablation size, tumor size, tissue condition, output level, controlmethod type, and other factors. The set time can be a function of theactive tip length of the electrode. The set time can be a value selectedfrom the range 0-30 minutes. In some embodiments, the stopping criteriafor the ablation process can include a criteria based on one or more ofthe following parameters: the total energy delivered to the tissue, thetotal aggregate up-time duration, and other parameters, thetime-integrated power, the time-integrated squared RMS current. Forexample, the diminishing output level, diminishing up-time durations,and increasing down-time durations over steps 314, 315, 316, 317, 318,319, 320, 321, and 322 are an indication of diminishing heating powerand a diminishing rate of lesion size increase; thus, in someembodiments, these factors can be used by an automatic controller and/oruser to determine a stop time for the ablation program.

In the example presented in FIG. 3, the control system starts with anablation output level 302 that is conservatively below the equilibriumvalue. This provides the advantage of avoiding overheating the tissueand inducing irreversible or slowly-reversible tissue changes that canprevent, hinder, or slow the formation of a large lesion around a cooledelectrode tip. The control system then increases the output level toincrease lesion size, but does so at a rate slow enough for the tissueto respond measurably to the elevated output level. This has theadvantage of providing sufficient time for the control system tocalibrate to changing thermal dynamics while raising the output level,without too frequently boiling the tissue and thus interrupting lesiongrowth. The system can produce sufficiently high output levels tomaximize lesion size for larger RF electrodes, which can create largerRF heat lesions when properly powered. The control system interruptstissue heating in response to tissue boiling, as indicated by largeimpedance rises, to provide for tissue cooling and the dissipation ofhigh-impedance bubbles that hinder lesion growth. This allows tissueheating and lesion-size growth to continue even after excessive currenthas been driven into the tissue. Throughout the ablation process, thecontrol system adjusts the ablation output level in response to themagnitude and timing of impedance changes relative to heating phases andcooling phases. Ablation output levels (during “up times”) are reducedif previous output levels lead to tissue boiling too quickly forsufficient tissue heating to occur beyond the bubble zone. This has theadvantage of calibrating to the output level that the tissue can sustainwithout rapid boiling, which can change as the ablation process evolvesand the lesion size increases. The adjustment of the ablation level upand down in response to the timing of impedance spikes to find a stableoutput level for ablation has the advantage of delivering the an optimalamount of heating power into the tissue: high enough to increase lesionsize, but not so high as to frequently interrupt lesion growth withhigh-impedance tissue boiling. The control system adjusts the durationof cooling phases (“down times”) in response to the timing of impedancechanges. Cooling-time duration is increased if the duration of theprevious ablation phase was too brief to produce efficient lesion sizegrowth and/or if the duration of the previous ablation phase indicatesthat additional time is required to dissipate high-impedance bubblesaround the active tip. This has the advantage of increasing the coolingtime in response to rapid tissue boiling and the overall lesion time,both of which can be indicative of lesion size and bubble zone size. Thecontrol system is adapted to adjust the level of generator signal outputcurrent and the duration of up-times and down-times so that the sequenceof ablation and cooling settles down to a stable desired process. Theexample of FIG. 3 illustrates how the present invention enables astable, controlled, and reproducible ablation process with real-timevisual confirmation.

In the example shown in FIG. 3, the controller regulates the outputcurrent. In another example, the controller regulates power. In anotherexample, the controller regulates voltage. In one example, thecontroller regulates the ablation process by monitoring the impedanceand uses that to control the modulation of at least one of the outputparameters in the list of power, current, and voltage. In someembodiments, the initial current can be a value selected from the range500 mA to 3000 mA. In some embodiments, the initial current can be avalue less than 700 mA. In some embodiments, the initial current can begreater than 3000 mA. In some embodiments, the initial current canselected as a function of the cooled electrode active tip length, forexample, 500 mA for a 1 cm tip, 1000 mA for a 2 cm tip, 1400 mA for a 3cm tip, 1800 mA for a 4 cm tip, 2000 mA for a 5 cm tip. For example, theinitial current can be selected as 2200 mA for a cluster of threeparallel cooled RF electrode, each with a tip exposure between 3 and 4cm, and equally spaced by 1 to 2 cm.

In some embodiments, as in the embodiment of FIG. 3, the size of thestep increments and decrements can each be configured to determine agenerator output level, eg ablation current, that the tissue around theelectrode active tip can sustain to maximum the heat lesion size. Insome embodiments, as in the embodiment of FIG. 3, step decrements andstep increments are the same amplitude. In some embodiments, the stepdecrements are smaller than the step increments to provide for greaterprecision in determining a stable output level for ablation. Forexample, the step decrement can be 50 mA and the step increment can be100 mA. In some embodiments, the step increments are smaller than thestep increments. In some embodiments, the step increment can be a valueselected from the range 0-200 mA. In some embodiments, the stepdecrement can be a value selected from the range 0-200 mA. In someembodiments, the step increments and decrements can be greater than 200mA. In some embodiments, the step increments and decrements can changeduring the ablation process, for example, reducing in size to refineoptimization of the output level. In some embodiments, the stepdecrements can be inversely proportional to the duration of thepreceding up-time and/or the preceding up-time step increments; oneadvantage of this is that the output level can be refined more preciselyif the preceding output level was sustained for a longer period withoutboiling. In some embodiments, the step time for output level incrementscan be a value selected from the range 0-2 minutes. In some embodiments,the step time can be longer than 2 minutes. In some embodiments, theoutput level can be increased during the up time in a manner differentfrom step increments, such as a constant-rate ramp, a concave ramp, aconvex ramp, or a combination of different ramp shapes. For example, theoutput level can be ramped at a rate of 5 mA/sec after 60 seconds ofelapsed up time. For embodiments wherein the output level is increasedas a ramp, the size of the step decrement can be influenced by aparameter of the ramp, such as the rate of the ramp, or the amount ofoutput level increase during a final duration of the ramp.

In some embodiments, the initial down-time duration can be a valueselected from the range 0-40 seconds. In some embodiments, the initialdown time can be a value greater than 40 seconds. In some embodiments,the down-time duration increment can be a value selected from the range0-10 seconds. In some embodiments, the down-time duration increment canbe a value greater than 10 seconds. In some embodiments, the down timecan be set and adjusted by the generator control by a different methodthan the one shown in FIG. 3. For example, the down time can be afunction of the preceding up-time duration, for example, proportional tothe preceding up-time duration. For example, the down time can increasein a predetermined schedule as an increasing function of one or more ofthe values selected from the following list: total elapsed time, numberof up-time pulses, total elapsed up-time duration, and other parameters.For example, the duration of the down time can be incremented by thedown-time duration increment after every up time. For example, the downtime can be affected by the dynamics of the impedance signal 350. Forexample, the down time can be affected by the dynamics of the impedancesignal 350 during the down time. For example, during the down time, thegenerator can monitor the impedance signal for a large drop from anelevated value, followed by a stabilizing impedance signal. Thisimpedance “cooling pattern” can be observed following every impedancespike in signal 350 of FIG. 3, and can be indicative of the size of theheat lesion, the extent of the bubble zone, and therefore the coolingtime required before the next up time should be optimally initiated. Inone example, the generator can prevent termination of the down timeuntil the impedance cooling pattern is detected. In one example, thegenerator can prevent termination of a down-time period until both theimpedance cooling pattern is detected and the minimum down-time durationhas elapsed. In one example, the generator controller can determine theduration of each down time as the sum of (1) the time it takes for theimpedance cooling pattern to be detected, and (2) an additional durationthat can be either fixed or a variable function of measured ablationparameters. One advantage of a non-zero output level during the downtime, such as shown by downtime 306 in FIG. 3, is that it provides forcontinued impedance measurement 350.

The parameters of the control process presented in one specific examplein FIG. 3 can vary depending on the specific clinical situation.Selection of parameters can include consideration of target size,electrode geometry, durations of up-times and down-times, generatorsignal output parameters, total duration of HF exposure and other factorin order to optimize to stability of the process and desired clinicaloutcome.

Referring now to FIG. 4, one embodiment of a pulsing method forimpedance-based control of a cooled-RF ablation electrode is presentedas flow chart in accordance with several aspects of the presentinvention. In some embodiments, the method in FIG. 4 can executed by thegenerator systems presented in FIG. 1 and FIG. 2. In some embodiments,the ablation measurements presented in FIG. 3 can be produced by amethod similar to that presented in FIG. 4 with the followingmodifications: (1) The coolant tests in steps 405, 410, 415, and 420 areeither omitted, or occur before time zero on axis 390 of FIG. 3; and (2)step 460, in which the output current step size is adjusted, is omitted,and step 455 transitions directly to step 425.

In initial step 400, the method begins by initializing with parametersthat can be user-selectable. The lesion time (also referred to as “settime”) is typically in the range 2-20 minutes, but can be any non-zerovalue. The initial ablation current (also referred to as the “initialset current” for the up time) can be any non-zero current up to themaximum current output level of the generator, typically in the range500-2500 mA. In some embodiments, a user-selectable maximum current canbe included as well. In step 405, parameters are initialized that mayvary during the ablation session, including the step size forset-current increments and decrements, and the step time for set-currentincrements. In some embodiments, a maximum set current can also be setin step 405, and that maximum set current can be user-selectable,factory set, set by the generator as a function of the initial setcurrent, or a combination of these. In some embodiments, the step sizecan be a value in the range 0-200 mA or more. In some embodiments, eachstep can be a step in Power and the step size can be a value in therange 0-50 Watts or more. In some embodiments, each step can be a stepin Voltage and the step size can be a value in the range 0-50 Volts ormore. In some embodiments, each step can be in units of some measurementof the signal output level. In some embodiments, the elapsed up-timebefore a step increase can be a value in the range 0-120 sec or longer.In some embodiments, the step size and duration can be configured toallow for optimization of a stable output level for given electrodegeometry and construction and tissue conditions. One advantage ofcontrolling the current of the RF output level is that, for a givenelectrode active tip geometry, a set current can regularize the currentdensity around the active tip across different ground pad placementsrelative to the electrode position in the body; in contrast, a setvoltage or set power, the local heating power near the active tip willvary with the position of the ground pad(s) on the body due to differentdegrees of ohmic voltage/power drops in the tissue between the ablationelectrode active tip and the ground pad(s). Another advantage ofcontrolling the current of the RF output level delivered to a monopolarablation electrode is that control and monitoring of ground pad currentsis simplified by having a controlled total ground pad current (which isequal to the electrode current in a monopolar configuration). In step410, the generator output is set to a very low level that provides forimpedance measurement, and that is configured not to raise the electrodetemperature, even in the absence of coolant flow. The pump runs forsufficient time for electrode coolant to flow from the coolant reservoirinto the electrode. In some embodiments, the duration in step 410 can bea value in the range 5-60 seconds, or a value larger than 60 seconds forvery long coolant tubes and/or very slow pump speed. In step 415, thegenerator checks whether the electrode is properly cooled. If there is aproblem with the coolant or coolant flow, the temperature will read avalue close to the tissue temperature in which the electrode is placed,a coolant error 420 will be signaled to the user, and the ablationprogram terminated 428. If the temperature in step 415 is below 30 degC., then the ablation phase of the program begins in step 425. In someembodiments, step 410 and 415 and combined so that the process proceedswith step 425 as soon as the temperature is in a range indicatingsuccessful cooling (less than 30 deg C.) within the maximum pump time(45 seconds), and otherwise signals an error 420. On the first visit tostep 425, the output level is rapidly ramped up to the initial ablationcurrent level at a rate of approximately 100 mA/sec. An example of thisis illustrated by ramp 301 to initial ablation-current level 2000 mA inFIG. 3. An instance of “up time” begins as the process transitions fromstep 425 to 430. In step 430, the output level is incremented byapproximately 50 mA or 100 mA (depending on the present value of the“current step”, which is set in steps 405 and 460) after every 30seconds of the time elapsed since the end of step 425, which is theelapsed duration of the present “up time”. One example of this processis illustrated by the RF current curve 300 as it increases through steps302, 303, 304, and 305 in FIG. 3. Step 435 is a check on the totalablation program duration, which terminates the ablation program 428after the ablation phase of the program has operated for at least theduration of the “lesion time” setting. In some embodiments, othertermination criteria can be included in step 435, such as the criteriathat one of the following quantities exceeds a specified threshold: thetotal heating energy delivered in units Joules, the sum of the durationsof all up-times, the number of up-time pulses; one advantage of usingthese quantities in the termination criteria is that they relate to theaggregate signal output delivered to the tissue. In some embodiments,the termination criteria of step 435 can include the criteria that oneof the following quantities is less than a specified threshold: theduration of the down time (for methods in which the down timeincreases), the current level during the up time (for processes that candecrease the current level during the up times), the average currentover the latest up time and down time (for processes that can decreasethe current level during the up times); one advantage of including thesekinds of criteria is that they can reflect a decrease in the heatingpower delivered by the generator, and thus, a decrease in the amount oflesion size growth for the additional ablation time investment. In someembodiments, a termination criterion in step 435 can be influenced by adecline in the output level, a decline in the average output level,and/or an increase in the down time duration; one advantage of thesefactors for influencing a termination criteria is that can indicate adecrease in the efficiency of the ablation process and thus, diminishingreturns in lesion size growth for continued ablation. Step 440 is acheck on the termination criteria for the present up-time phase. If animpedance spike is detected in step 440, the process proceeds to step445 thus starting a down-time phase. If an impedance spike is notdetected in step 440, the up time continues. The cycle of steps 430,435, and 440 can correspond to one instance of “up time” (which can alsobe a referred to as an “on period” or “up period” or “on time” or“pulse”) in which the RF signal level is configured to heat tissue andincrease the volume of heated tissue by means of the ablation electrode.In step 445, the output level is reduced from the level of the precedingup time to a low level configured to provide for tissue cooling andbubble zone dissipation. In step 445, the programmed duration of thedown time, which can be referred to as the “cooling time”, is increasedif the duration of the preceding up time is less than 10 seconds, aduration configured to indicate that additional cooling time is requiredbetween ablation pulses (which are also known as “up times”, “on times”,“up periods”, or “on periods”). The cooling time was initialized in step405. By means of step 445, the cooling time increases with the number ofshort “up times”. This has the advantage that the cooling time isadjusted in response to evolving tissue conditions throughout theablation process. An example of this adjustment of the cooling time isillustrated by the down time 315 and down time 319 in FIG. 3. In someembodiments of step 445, the cooling time duration can be increased ordecreased as a function of one or more of the following parameters: theduration of the final output-level step of the previous up time, theduration of the previous up time (measured here by the “ablationtimer”). In some embodiments of the step 445, the change in the coolingtime is inversely proportional to the duration of up time (measured bythe value on the “ablation timer”). In some embodiments of step 445, theduration 10 sec can be a different value, for example, a value selectedfrom the range 0-30 sec or longer. In step 450, the generator controllerallows the cooling time to elapse. In step 455, it is determined whetherthe target current for the next up-time will be equal to, or lower than,the target current of the previous up-time, based on the duration of thefinal current step of the previous up-time. An example of this downwardadjustment is illustrated by the current measurement 300 in FIG. 3. Insome embodiments of step 455, the ablation current level can beincreased or decreased as a function of one or more of the followingparameters: the duration of the final output-level step of the previousup time, the duration of the previous up time. In some embodiments ofthe step 455, the change in the ablation current level is proportionalto the duration of the last electrode current-step increase. In someembodiments of step 455, the duration 10 sec can be a different value,for example, a value selected from the range 0-30 sec or longer. In step460, it is determined whether to reduce the magnitude of subsequentupward and downward changes in the output current, based on the durationof the final current step of the previous up-time, which can indicaterapid boiling in response to the last output-level adjustment. Step 460is one example of a process configured to increase the precision withwhich the output level is adjusted when there is an indication that thesize of the last adjustment was too large. In some embodiments of step460, the step increments and decrements can be changed independently. Insome embodiments of step 460, an adjustment to the frequency with whichcurrent-step increments are made during step 430. In some embodiments ofstep 460, amplitude of the current step can be proportional to theduration of the last up time. In some embodiments of step 460, the time“10 sec” can be a different value, such as a value in the range 0-30seconds or longer. In some embodiments of step 460, the current stepvalue “50 mA” can be a different value, such as any value less than thepresent current step value. In some embodiments of step 460, the currentstep value “50 mA” can be a different value, such as a value greaterthan the present current step value, but less than a maximum currentstep, such as a value of 200 mA or more. In some embodiments of step460, the current step value can increase or decrease from its previousvalue as a function of a measurement of an ablation parameter. Afterstep 460, in step 425, the generator controller steps the output levelto approximately the target current level for ablation, thus ending the“down time” and starting the next “up time” in step 430. Steps 445, 450,455, and 460 can represent one instance of “down time”, which is anexample of a period in which the controller configures the RF level toallow for cooling of heated tissue and/or dissipation of gas formed inthe tissue due to heating during the preceding “up time”.

One advantage of the impedance-based RF pulsing method for cooled RFablation presented in FIG. 4 is that the ablation output level, theduration of ablation pulses (which can be referred to as “up times” or“on periods”), and the duration of inter-pulse cooling periods (whichcan be referred as a “down times” or “off periods”) are adjusted inresponse to measured system parameters. One advantage of the cooled-RFablation program presented in FIG. 4 is that output level duringhigh-intensity ablation pulses is adjusted both upward and downward tomaximize the degree and duration of tissue heating throughout theablation process, without overheating tissue close to the electrodeactive tip into the boiling range too frequently. In some embodiments,automated checks for the program's termination criteria, eg step 435,for checks on system performance, and for error conditions typical of RFlesioning systems (such as open circuit, short circuit, temperaturesignal loss, and over temperature limit conditions) can be insertedthroughout the method presented in FIG. 4 to ensure timely reaction tothese conditions. For example, a check on the total running time of themethod can be included between step 445 and 450. It is understood thatthe order of some steps, such as 405 and 410, can be changed withoutaffecting the essential method. It is understood that some steps can becombined without affecting essential method. It is understood that someomitted without affecting the essential method. It is understood thatadditional controller behaviors can be include in the method presentedin FIG. 4, for example, temperature control. In some embodiments, theparameters of the method presented in FIG. 4 can take values in theranges presented in the text describing FIG. 3.

Referring now to FIG. 5, one embodiment of a method for tissue ablationusing an internally-cooled HF ablation probe is presented as a flowchart. The method in FIG. 5 can be one example of one control processautomatically executed by the generator presented in FIG. 1, and in thegenerator presented in FIG. 2. The method in FIG. 4 can be a specificembodiment of the method presented in FIG. 5. The process that producedthe ablation data in FIG. 3 can be a specific embodiment of the processpresented in FIG. 5. In some examples, the ablation probe can be an RFelectrode. In some examples, the ablation probe can be a MW antenna.

In step 500, parameters that influence the ablation process are set.These parameters can include target output level, initial output level,maximum output level, minimum output level, duration of the ablationprogram, parameters related to the timing of processes, parameters thatcharacterize the target tissue, parameters that characterize theablation probe, ablation probe type, tissue type, desired lesion size.One or of these parameters can be selected by the user. One of more ofthese parameters can be set by the factory. One or more of theseparameters can be selected user selection of a preset configuration ofsettings, for example, as user-customizable preset. In Step 505,parameters are set that may vary during the ablation process, forexample, in response to values measured during the ablation process.

In Step 510 and 515, the operation of the coolant system is checked. Ifthe checks indicate insufficient coolant operation, a user error isprompted in step 520, and the ablation program is discontinued in step528. In embodiment presented in FIG. 5, the coolant system is checked byholding the output at zero or a very low level, operating the coolantsystem pump, and checking for desired cooling of the ablation probe. Insome embodiments, other checks of the cooling system can be included inthe steps 510 and 515, such as checking the flow rate coolant flow,checking the coolant temperature directly, and checking that theablation probe temperature does not rise substantially when the ablationprobe is energized at levels capable of heating the tissue. In someembodiments, checks on coolant operation, such as steps 505 and 510, canbe performed either intermittently or continuously throughout theablation processes. For example, the controller can check that theablation probe temperature does not exceed an absolute upper limit or anupper limit relative to a baseline value, either throughout the ablationprocess, during up time, during down times, or at other times during theablation process.

Step 535 performs one or more checks of termination criteria for theablation program, and if one is successful, the ablation process isterminated in step 528. One example of a check of a terminationcriterion is checking that one of the following quantities exceeds itsrespective termination threshold: elapsed program time, elapsed timedelivering output levels capable of heating tissue, total heating energydelivered to the tissue, time-integrated power delivered to the tissue,time-integrated current delivered to the tissue, the duration of thedown time, an increase in the down time duration, a decrease in theablation output level, an indicator of lesion size, an indicator of thebubble zone size, the time it takes for the impedance to return to abaseline value after an impedance spike. One example of a check of atermination criterion is checking if one of the following quantities isless than its respective termination threshold: an average output level,an RMS output level, the output level during an up time, the outputlevel averaged over the most recent up time and down time, a movingaverage of the output level, the duration of the up time.

Steps 525, 530, 540 implement the “up times” (which can also be referredto as “up periods”, “on periods”, or “on times”, or “pulses”) of theablation process, wherein signal output is delivered to the ablationprobe at a level or levels that are capable of producing tissueablation, heating tissue, and increasing the size of the ablationvolume. In one example, when step 525 is executed for the first time,the initial output can be set to a level configured to be conservativelybelow the expected steady-state output level for the present ablationprobe and tissue configuration. For example, the initial output levelcan be set in steps 500 and/or 505 by either a user, factory settings,or both. In another example, during the first execution of step 525, theoutput level can be configured to be equal to the steady-state ablationoutput level. In another example, during the first execution of step525, the output level can configured to be greater than to thesteady-state ablation output level. In step 530, the output level isincreased. For example, in step 530, the output level increase can beconfigured to raise the output level slowly to determine a steady outputlevel for the majority of the ablation process. For example, in step530, the output level can be increased to adjust an erroneously lowinitial output level, which in one example, can be due to a user errorin selection of settings values in step 500. In step 530, the increasein ablation output level can be configured to test the tissue responseto higher output levels. In some embodiments of step 530, the outputlevel is not increased, but rather held at a constant value. In step540, the HF generator controller checks for evidence of boiling inheated tissue. If boiling is not detected, the output level ismaintained at levels capable of tissue ablation in step 530. If boilingis not detected, then the generator output level is reduced in step 545to halt the boiling and to allow for tissue cooling and dissipation ofhigh-impedance gas formed due to boiling. In some embodiments of 540,boiling is detected by the impedance rising above an impedancethreshold. In some embodiments that impedance threshold can be anpredetermined impedance value, an impedance value computed relative to astatistic of impedance measured during the ablation program, animpedance value that is a function of the initial impedance, animpedance value that is a function of the minimum impedance measuredduring the ablation program, an impedance value that is a function ofthe minimum impedance measured during the present up time, an impedancevalue that is determined based on the electrode type, an impedance valuethat is determined based on tissue characteristics, and other impedancevalues. In some embodiments of 540, boiling can be detected as afunction of one or more of the following measurements: voltage, current,power, impedance, temperature. In some embodiments of 540, boiling canbe detected by measurement of an electrical signal (such as animpedance, voltage, current, or power measurement) that is differentfrom the electrical signal that is producing the tissue ablation; forexample, this can be another electrical signal applied to the ablationelectrode, or it can be an electrical signal applied to another probe orprobes in or near the tissue being heated by the ablation electrode. Insome embodiments of 540, boiling can be detected by means of one or moretemperature measurements, which can either taken from a sensor within anablation probe, or from sensor that is nearby an ablation probe. In someembodiments of 540, boiling can be detected by means of one or moretemperature measurements distributed around the ablation probe. In someembodiments of 540, boiling can be detected by the efficiency ofradiative power transmission into the tissue. In some embodiments, suchas an embodiment in which the electrode voltage is regulated, boilingcan be detected by a drop in electrode power. In some embodiments, suchas an embodiment in which the electrode voltage is regulated, boilingcan be detected by a drop in electrode current. In some embodiments,boiling can be detected by an indication of the volume and/or density ofvapor formed in the tissue around the ablation probe due to tissueheating. The test for boiling in step 540 is one example of criteria forending an “up time” in response to an indication that the size of thevolume of ablated tissue cannot be substantially increased by continuedapplication of a high signal output level to the ablation electrode,because boiling or an almost boiling condition in some of all of thetissue around an electrode active tip can produce a high impedance thatprevents substantial tissue heating beyond the location of boiling.

In steps 545 and 550, the generator controller reduces the output levela period of time (the “cooling time”, which can also be referred to asthe “down time”, “off time”, “off period”, “down time”, “down period”,“inter-pulse time”, or “inter-pulse period”) to allow for the reversalof tissue boiling detected in step 540. The output level set in step 540can be a predetermined value, a fraction of the ablation output level, avalue determined by measurement of the present tissue to provide forcooling, zero, a small value, a value less than 1 Watt, or anothervalue. The period of time during which the tissue cools can be apredetermined value, a fixed value, a computed value, a value thatincreases as the ablation process proceeds, a value that is affected bymeasurement during an ablation phase (ie “up time”), a value that isaffected measurements during a cooling phase (ie “down time”), a valuethat is affected measurements collected during step 545, a value that isproportional to the preceding up time. The cooling time can beconfigured to produce a stable ablation process. The cooling time can beconfigured to the particular time required for cooling of the heatedtissue. The cooling time can be configured to provide for dissipation ofvapor formed due to tissue heating. The cooling time and the level of RFsignal during the cooling time can provide for cooling of heated tissueto a degree configured to allow for further increase in the volume ofheated tissue in the subsequent ablation phase (“up time”). In someembodiments, the cooling time can be increased, decreased, or bothincreased and decreased in response to measured parameters, for example,the measured duration of previous up times and down times. In someembodiments, the cooling time can be increased and/or decreased over thecourse of the ablation process to determine a stable value of thecooling time and/or other output signal characteristics. In someembodiments, the down time can be influenced by a temperaturemeasurement at distance from the electrode active tip. In someembodiments, the down time can be influenced by ultrasound data.

In 555 and 560, the generator controller adjusts the ablation outputlevel which will be delivered to the ablation probe in step 525, and theschedule by which the ablation output level is varied during in step530. For example, in step 555 the ablation output level can be reducedin response to measured parameters during the preceding ablationprocess. For example, in step 555, the ablation output level can bereduced to prevent rapid tissue boiling. For example, in step 555, theablation output level can be reduced to produce a stable ablation outputlevel. For example, in step 555, the ablation output level can bereduced to maximize lesion size. For example, in step 555, the ablationoutput level can be reduced to more rapidly increase lesion size. Forexample, in step 555, the ablation output level can increased by adegree influenced by the duration of the immediately preceding up time.For example, in step 555, the ablation output level can increased by adegree that increase as the duration of the preceding up time increases.For example, in step 555, the ablation output level can increased if thepreceding up time exceeded a threshold; in one example, the thresholdcan be configured to a value that indicates the rate of heating duringthe preceding up time was too low. For example, in step 560 one or ofthe following parameters can be changed either for the output-levelincrease in step 530, for the output-level decreases in step 545, orboth: the amplitude of change, the rate of change, the frequency withwhich changes are made. For example, in step 560 stepped changes in theoutput level can be increased or decreased as a function of measuredablation parameters.

The steps 525, 530, 540, and cycles thereof can produce one instanceof“up time” in an ablation process. The steps 545 and 550 produce oneinstance of “down time” in an ablation process. In one example, theablation program in FIG. 5 alternates between up times and down times,adjusts the ablation output level upward and downward, adjusts the downtime duration upward and downward, for the purpose of determining stableoutput signal for tissue ablation. In one example, the ablation programin FIG. 5 alternates between up times and down times, adjusts theablation output level upward and downward, adjusts the down timeduration upward and downward, for the purpose of maximizing heat lesionsize. In one example, the ablation program in FIG. 5 alternates betweenup times and down times, adjusts the ablation output level upward anddownward, adjusts the down time duration upward and downward, for thepurpose of increasing the speed for heat lesion formation. In oneexample, the ablation program in FIG. 5 alternates between up times anddown times, adjusts the ablation output level upward and downward,adjusts the down time duration upward and downward, for the purpose ofablating a target bodily structure, such as a tumor.

In some embodiments of the RF pulsing method shown in FIG. 5, the signallevel during the on periods are held constant by instances of step 530,and increased by instances of step 555 by an amount influenced by theduration of a preceding on period. In some embodiments of the pulsingmethod shown in FIG. 5, the signal level during the on periods isincreased during instance of step 530 as a function of the duration ofthe present on period, and not increased by instance of step 555. Insome embodiments of the pulsing method shown in FIG. 5, the signal levelduring the on periods are increased during instance of step 530 as afunction of the duration of the present on period, and increased byinstances of step 555 by an amount influenced by the duration of apreceding on period.

In some embodiments, the method of FIG. 5 can be applied to a non-cooledablation probe, such as an ablation probe that does not include atemperature sensor, a non-cooled ablation probe by means of which it isdesired to maximize the heat lesion around the ablation probe, anon-cooled RF electrode, a non-cooled and non-temperature-monitoring RFelectrode, a non-cooled MW antenna, or a non-cooled andnon-temperature-monitoring MW antenna. In such embodiments, steps 510,515, 520 can be omitted, because they relate to the flow of coolantwithin the ablation probe. Note that, for both internally-cooled andnon-internally-cooled HF ablation probes, tissue heated by a HF ablationprobe will cool passively when the applied HF signal output is loweredsufficiently (eg turned off) due to the cooler surrounding tissue.

One advantage of the method presented in FIG. 5 is that the ablationoutput level is adjusted both upward and downward in response toevidence of tissue boiling to produce a maximal, stable HF ablationprocess. One advantage of the method presented in FIG. 5 is that thesize of the ablation zone can be maximized. One advantage of the methodpresented in FIG. 5 is that the ablation output level is adjusted bothupward and downward to calibrate to particular tissue conditions andablation probe type. One advantage of the method presented in FIG. 5 isthat the duration of inter-pulse cooling periods are adjusted inresponse to measurements of the ablation process. One advantage of themethod presented in FIG. 5 is that HF signal level during on periods,the duration of on periods, and the duration of off periods are adjustedto increase the volume of heated tissue maximally by approaching orexceeding the boiling temperatures within heated tissue throughout theablation process. One advantage of the method presented in FIG. 5 isthat HF heating energy is delivered in high-intensity pulses to increaseheat lesion size and avoid the hindering effect of tissue boiling. It isunderstood that some steps in the flow chart of FIG. 5 can berearranged, combined, omitted, or added without affecting one or aspectsof the present invention embodied in FIG. 5. It is understood that errorchecks, user notification steps, and termination criteria checks can beadded to the method in FIG. 5. It is understood that additionalcontroller behaviors can be included in the method presented in FIG. 5,for example, temperature control.

Referring now to FIG. 6, one embodiment of a HF ablation system ispresented as in a block diagram, in accordance with several aspects ofthe present invention. The system presented in FIG. 6 can be oneembodiment of the system presented in FIG. 1. The system presented inFIG. 6 is one example of a system that can generate the ablationprocesses and measurements presented in FIG. 3. In some embodiments, themaster controller 603 can execute the process presented in FIG. 4. Insome embodiments, the master controller 603 can execute the processpresented in FIG. 5. In some embodiments, FIG. 6 presents one example ofa system for tissue ablation that includes a radiofrequency signalgenerator 605, a user interface 602, an ablation electrode 650, and atleast two ground pads 621, 622, 623, 624; wherein current from theradiofrequency signal 605 generator can flow between the electrode 650and each ground pad if the electrode and the ground pad are in contactwith the same living body 690; wherein the system measures the currentflowing through each ground pad (by means of measurement devices MG1,MG2, MG3, MG4). In some embodiments, the user interface 602 or itsgraphical display 601 can include a display of a parameter of thecurrent of a ground pad.

The generator 600 is connected to one or more cooled ablation probes 650inserted into patient body 690. The coolant pump 630 can be connected tothe generator controller 604 via control line 634, and can supplycoolant to the ablation probe 650. The generator 600 can monitor andcontrol the coolant pump 630 via connection 634. The ultrasound imagingdevice 640 can be connected to the generator user interface 602 viacontrol line 644, and to transducer 645 which can image the electrode650 in body 690. In some embodiments, the ultrasound machine caninterface with the generator controller. Ablation probe 650 has activetip 651.

Controller 604 is connected to HF power supply 605, master controller603, probe and ground pad interface 608, user interface 602. In someembodiments, the user interface can include display and interfaceelements that are familiar one skilled in the art, includingnon-graphical user-interface elements. The user interface 602 isconnected to graphical display 601. Graphical display 601 can be adisplay monitor or a touch screen display. Graphical display 601 canpresent ablation parameters and measurements graphically to the user,such as the graphs 102A, 102B, 102C, 102D, 102E, 102F, 102G, 102H, 119A,119B, 119C in FIG. 1, or the graphs presented in FIG. 3. The interfaceelement 608 can provide measurements of the HF output delivered to theablation probe 650 and of temperatures and other signals sensed by theablation probe 608. The combination the HF supply 605, controller 604,master controller 603, probe measurement and interface element 608, userinterface 602, and graphical display 601 provides for automatic controlof the ablation process and for graphic display of parameters, forexample as described in FIG. 1, FIG. 2, FIG. 3, FIG. 4, and FIG. 5. Theuser interface 602 and graphical display 601 provide a graphical userinterface. The master controller 603 connects to the control computer604 to control its functions, to the graphic user interface 601, 601 toallow the user to see and/or to adjust the controller settings; and tothe probe interface element 608 to monitor and control interface to theablation probe 608 and ground pads 621, 622, 623, 624. In someembodiments, the ultrasound imaging machine 640 and the controller 604can be connected, and the controller 604 can adjust the ablation processautomatically based on data from the ultrasound machine, such asestimates of tissue temperature, estimates of lesion size, and estimatesof lesion size based on hyperechoic bubbles.

FIG. 6 shows, in one example, an electrode and ground pad interface 608which is connected to the HF supply 605, the computer controller 604,and the graphical user interface 601 and 602. The element 608 connectsto electrode 650 and ground pads 621, 622, 623, 624. The elementprovides measurements of the signal output delivered to the electrode650 and to each of the ground pads 621, 622, 623, 624, as well asmeasurement of the electrode temperature or temperatures. The interface608 includes switches 611 labeled SG1, SG2, SG3, SG4 that can connectand disconnect the one or more ground pads 621, 622, 623, 624 from thegenerator supply 605. The switches 611 can connect and disconnect eachground pad from supply 605 as clinically desired and/or to control thecurrent flowing to each pad. The switches 611 can be closed to create anelectrical circuit through the patent between the electrode 650 and oneor more ground pads 621, 622, 623, 624. The interface 608 includesswitch SE1 that can connect and disconnect the one or more electrode 650from the generator supply 605. The switch SE1 can turn electrode 650 onand off during pulsing sequences. The control line 612 can also be usedto enable and disable the power supply 605 to turn the electrode 650 onand off during pulsing sequences. In some embodiments, an active circuitelement can be put in series with each ground pad switch, such as SG1,wherein the active circuit element produces an adjustable resistancethat can be adjusted by the controller to change the distribution ofcurrent among the connected ground pads. Measurement element MV1 can bea high-impedance voltage measurement device that measures the outputpotential generated by supply 605. ME1 610 can be a low-impedancemeasurement device through which HF signals from supply 605 flow toelectrode 650. ME1 can measure the current flowing to electrode 650 andthe one or more temperatures measured by electrode 650. Measurementelements MG1, MG2, MG3, and MG4 connect to ground pads 621, 622, 623,and 624, respectively, and each can be a low-impedance device throughwhich HF current flows to the connected ground pad, and by whichground-pad-specific current can be measured. The voltage and currentmeasurements from MV1 and ME1 respectively can be used to compute animpedance and power for electrode 650. The measurements from MV1, ME1,MG1, MG2 MG3, and MG4 can be used to compute voltages, current, powers,and impedance related to each or any of the electrodes 650 and groundpads 621, 622, 623, 624. The controller 604 and master controller 603can use measurements from interface element 608 to control generatoroutput. Measurements from element 608 can be displayed by user interface601 and graphical display 601. The interface element 608 and itscomponent switches 611 and measurement devices 610 can be controlled bythe controller 604, master controller 603, and user interface 602.

When electrode 650 and ground pad 621 are in contact with living body690, electrode switch SE1 is closed, ground pad switch SG1 is closed,and power supply 605 is active, then electrical current can flow betweenthe electrode 650 and ground pad 621 through living body 690; however,when the switch SG1 is open, current from supply 605 is prevented fromflowing through ground pad 621. When electrode 650 and ground pad 622are in contact with living body 690, electrode switch SE1 is closed,ground pad switch SG2 is closed, and power supply 605 is active, thenelectrical current can flow between the electrode 650 and ground pad 622through living body 690; however, when the switch SG2 is open, currentfrom supply 605 is prevented from flowing through ground pad 622. Whenelectrode 650 and ground pad 623 are in contact with living body 690,electrode switch SE1 is closed, ground pad switch SG3 is closed, andpower supply 605 is active, then electrical current can flow between theelectrode 650 and ground pad 623 through living body 690; however, whenthe switch SG3 is open, current from supply 605 is prevented fromflowing through ground pad 623. When electrode 650 and ground pad 624are in contact with living body 690, electrode switch SE1 is closed,ground pad switch SG4 is closed, and power supply 605 is active, thenelectrical current can flow between the electrode 650 and ground pad 624through living body 690; however, when the switch SG4 is open, currentfrom supply 605 is prevented from flowing through ground pad 624. It isunderstood that when a switch (such as SG1, SG2, SG3, or SG4) is opensome de minimus amount of current from the power supply 605 can flowthrough its attached ground pad (such as 621, 622, 623, 624,respectively) due to, for example, capacitive and inductive couplingamong the many ground pads, electrodes, cables, wires, and otherelectrical circuit elements in the system; in this case, it can still besaid that current from the power supply 605 does not substantially flowthrough the ground pad (such as 621, 622, 623, 624, respectively).

The generator 600 can provide a jack to connect each electrode 650 andground pad 621, 622, 623, 624 to their respective output lines. JacksE1, G1, G2, and G3 in FIG. 1A are one example of such jacks. In someembodiments, the order of the measurement element and the switch can bereverses along the output line leading to the attached electrode orground pad; for example, switch SE1 can be positioned between electrode650 and measurement device ME1.

In some embodiments, the generator chassis 600 can include the pump 630.In some embodiments, the generator chassis 600 can include theultrasound imaging unit 640. In some embodiments, elements contained inhousing 600 as shown in FIG. 6 can be housed in two or more physicallyseparate chasses. In some embodiments, ultrasound imaging data fromultrasound machine 640 is displayed on graphical display 601. In someembodiments, the ultrasound imaging device can be controlled usinggenerator user interface 602, including with input from the generatorgraphical display 601, master controller 603, and/or controller 604. Insome embodiments, the ultrasound machine 640 can control and/or displaydata from generator 100 via data connection 644. In some embodiments,the user interface 602 can generate a data file for an ablation session.In some embodiments, the user interface 602 can generator a data filethat contains both ultrasound and HF ablation data.

In some embodiments, the HF supply 605 can be a HF voltage source. Insome embodiments the power supply 605 can be an RF power supply. In someembodiments the power supply 605 can be an MW power supply. The powersupply 605 can be enabled and disabled by controller 604 via controlconnection 612. The output level of the power supply 605 can be adjustedby the controller 604 by means of control connection 612. In someembodiments, power supply 850 can generate additional RF and stimulationpotentials. In some embodiments, the power supply can include multipleelectrical sources which are electrically isolated from each other. Insome embodiments, current flows between a first electrode and ground padpair connected to generator 800, and current flows between a secondelectrode and ground pad pair connected to generator 800, and the firstpair and the second pair are electrically-isolated from each other.

In some embodiments, power supply 850 can include an electrical supplythat produces a direct current (DC) potential. The DC supply can beactive at the same time as the RF supply and thereby add adirect-current offset to the RF signal. For example, the cathode of theDC supply can be connected to an electrode, and the anode of the DCsupply can be connected to one or more ground pads, to implement bimodalelectric tissue ablation (BETA) which is theorized to increase hydrationof tissue near the electrode, slow tissue desiccation, and therebyincrease lesion size. In some examples, the DC supply can supply aconstant DC voltage. In some examples, the DC supply can supply aconstant DC current. In some examples, the DC supply can supply aconstant DC power. One advantage of performing BETA with a constant DCcurrent is that the effect of the DC signal at the electrode is notaffected by voltage drops and power losses remote of the electrode (suchas in the impedance between the skin surface and the ground pad) in thecircuit between the anode and cathode of the DC supply.

In some embodiments, the ablation probe 650 is an MW antenna and theground pads 621, 622, 623, 624 can be omitted. In some embodiments, theablation probe 650 can be an RF electrode. In some embodiments, theablation probe 650 can be multi-prong RF electrode. In some embodiments,the ablation probe 650 can be a cluster RF electrode, wherein theelectrode includes multiple independent shafts with each an active tip.In some embodiments, the ablation probe 650 can be multiple RFelectrodes connected to the generator output using a splitter cable. Inembodiments wherein multiple electrodes are connected to measurementelement ME1, ME1 can monitor the temperature signal for each electrode.In some embodiments, the generator output signal line 607 is split intoa multiplicity of lines, each of which contains a switch SE1 andmeasurement element ME1 configured to conduct current to, measure thecurrent flowing to, and measure the temperature from one of amultiplicity of electrodes 650; this provides for independent switching,measurement, and control of the output signal to multiple electrodes.For example, this can be used to independently pulse the generatoroutput to each of multiple electrode 650.

Referring now to FIG. 7, one embodiment of a HF system for tissueablation is presented as a schematic drawing in accordance with severalaspects of the present invention. In some embodiments, the HF system canperform RF tissue ablation. In some embodiments, the HF system canperform MW tissue ablation. In one aspect, FIG. 7 presents one exampleof a tissue ablation system 700 that includes a HF generator and anultrasound imaging machine in a single chassis. In one aspect, the HFgenerator 700 one example of a HF generator is configured for bothultrasound imaging and tissue ablation. In one aspect, the generator 700presents one example of a generator that can perform ultrasound imagingand that can produce both a HF signals for ablation, and nervestimulation signal for electrical stimulation of nerves. In one aspect,HF generator 700 presents one example of a HF generator that includes adisplay of ultrasound imaging data 708 and of HF ablation parameters712, 718. In one aspect, FIG. 7 presents one example of a system 700 forHF tissue ablation that includes one or more cooled HF probes, areal-time graphical display of measured parameters 718, a controllerthat implements a method for impedance-based control of the one or morecooled HF probes, a controller that implements temperature control ofone or more cooled HF probes, a controller that implements voltagecontrol of one or more cooled HF probes, a controller that implementscurrent control of one or more cooled HF probes, a controller thatimplements power control of one or more cooled HF probes, and a graphicdisplay of ultrasound imaging data 708. In one aspect, FIG. 7 presentsone example of a system 700 for HF tissue ablation that includes agraphic display on which impedance (dashed line) and HF signal outputlevel (solid line; eg current, voltage, power) are plotting in real timeon the same time axis 718 for each of at least one generatorablation-probe outputs (eg ablation electrodes); in the example of FIG.7, the signal output level plotted in voltage (solid line). In oneaspect, FIG. 7 presents one example of a system 700 for HF tissueablation that includes a graphic display on which impedance (dashedline), HF signal output level (solid line), and temperature (dottedline) are plotted in real time on the same time axis 718 for each ofmultiple ablation electrodes, which can include cooled electrodes,cooled electrode with extension-tip temperature monitor, standardelectrodes, non-cooled electrodes, non-temperature-sensing electrodes,non-temperature-sensing and non-cooled electrodes. In one aspect, thegenerator 700 is one example of a generator that includes an RF signalgenerator and a nerve stimulation signal generator, and that can connectto two or more reference ground pads 735, 736. In one aspect, thegenerator 700 is one example of a generator that includes an RF signalgenerator and a nerve-stimulation signal generator, that can perform RFablation at one or more ablation probes at the same time, that canconnect to two or more ground pads to carry return current from the oneor more ablation probes, and that can measure the current flowingthrough each of two or more reference ground pads.

The system 700 includes data ports 701, 702, 703 that provide for inputand output of data including procedure data, ultrasound data, ablationdata, and control signals; a lamp 704 that indicates active electrodeoutput; a mechanical button 705 that activates electrode output; amechanical button 706 that deactivates electrode output; a display touchscreen 710; ground pad jacks 731, 732 labeled “G1”, “G2”, that connectto ground pads 735, 736 via cables 733, 744, respectively, whereinground pads 735 and 736 are placed on the skin surface of patient 790;six electrode jacks labeled “E1”, “E2”, “E3”, “E4”, “E5”, and “E6”, forexample 741 and 746, that each connect to an electrode, such aselectrode 761 and 766; ultrasound jack 708D labeled “US” that connectsto ultrasound transducer 708F via cable 708E; and pump control andmeasurement connection 724 that connects to coolant pump 720. Standardelectrode 761 is connected to jack 741 via cable 751, and includes aproximal hub 761A, an insulated shaft 761B, and an active tip 761C,wherein the active tip 761C is placed near target nerve 791 in patientbody 790. Internally-cooled electrode 766 is connected to jack 746 viacable 756, and includes a proximal hub 766A, an insulated shaft 766B,and an active tip 766C, wherein the active tip 766C is placed neartarget nerve 796 in patient body 790. In one example, electrode 766 caninclude a temperature-measuring extension tip. Coolant from fluidreservoir 721 is pumped by pump head 722 of pump 720 through tubing766D, into electrode 766 to cool active tip 766C, through tubing 766E,and into collection container 725. In FIG. 7, each electrode targets anerve, such as a spinal nerve carrying painful impulses. In otherembodiments, one or more of the electrodes, or all the electrodes, cantarget tumors, such as tumors in the liver, kidney, lung, or anotherorgan or bone. In some embodiments, electrodes can target different typeof bodily structures. In some embodiments, all the electrodes can becooled electrodes. In some embodiments, an electrode can be of one typeselected from the list: a standard RF electrode, an electrode placedwithin an RF cannula, a temperature-sensing electrode, a cooledelectrode, a cooled electrode including an extension-tip temperaturesensor, a multi-tined electrode, a side-output electrode, and othertypes of RF electrodes known to one skilled in the art. In the followingdescription, electrodes and ground pads can be referred to by theirrespective jack label, such as “E6” for electrode 766. Pump 720 includesuser control 723, two pump heads such as head 722, and two fluidreservoirs such as fluid bag 721.

The graphic display 710 includes a control for each electrode, such ascontrol button 711 for electrode E1, with which the electrode can beactivated and deactivated, and with which the output polarity and otherelectrode-specific settings can be changed by the user; digitalmeasurement displays for each electrode, such as displays 712, includingtemperature, impedance, elapsed lesion time, voltage, current, andpower; a digital measurement display for each ground pad current, suchas display 713; graphical measurement displays for electrode and/orground pad readings, such as graph 718 of the temperatures, impedances,and voltages of all electrodes plotted on the same time axis inreal-time and matching the digital displays of those measurements ineach electrode panel (eg 712); ultrasound controls 708A, 708B, 708C forcontrol of the ultrasound system; ultrasound image display 708 fordisplay of ultrasound imaging data collected by transducer 708E; RFgenerator controls, such as button 715, for timer reset, taking screenshots, entering clinical notes, printing procedure data, exportingprocedure data, transitioning to a menu screen, and selection amongvarious output control modes, including sensory and motor nervestimulation, peripheral electrical nerve stimulation (PENS), standardRF, cooled RF, and pulsed RF as used in the field of RF pain management;a control and display for ablation program settings 719; and a togglebutton for activating and deactivating electrode output 717. Thegraphical display 718 includes a label for each plotted line to identifythe electrode for which the line plots a measurement. In someembodiments, the graphs 718 can include a reading for the output levelof the each electrode, such as current, voltage, or power. In someembodiments, the graph 718 can include a line for the impedance for eachelectrode. In some embodiments, the graph 718 can include a line for thetemperature for each electrode. Real-time plotting on the same time axisof impedance and HF signal output level for each electrode can beimportant for non-temperature-sensing electrodes, for example E1 in FIG.7 (as indicated by the “--” indicator for “no temperature reading”712A), because the real-time graphic display can provide a clearindication of tissue boiling, such as by means of a rapid increase inimpedance, such as shown in one example by the impedance line plot forelectrode E4 on graphical plots 718. Real-time plotting on the same timeaxis of impedance and HF signal output level for each electrode can beimportant for a cooled RF electrode with a temperature-sensing extensiontip because the extension tip may not measure the maximum tissuetemperature, and the impedance signal relative to the signal outputlevel can provide an indication that the maximum tissue temperature isin the boiling range. Real-time plotting on the same time axis ofimpedance and HF signal output level for each electrode can be importantfor all electrode types to provide a signal to the physician of boiling,for example, in the case where a temperature sensor is malfunctioningand the temperature reading is not accurate. In some embodiments, thereal-time graphical plots for each electrode can be positioned on anindividual axis for each electrode, for example axes that are stackedside by side, for example aligned with each electrode display panel (eg712 for electrode E1). The settings panel 719 includes settings fortotal lesion time, voltage, temperature, and a selection forautomatic/manual control. These can take a variety of settings values.In some embodiments, the lesion time, temperature, and mode settings cantake values in the ranges described in relation to settings 106A, 106C,106D, respectively. In some embodiments, the voltage setting can take avalue in the range 0-200 V-RMS or higher. In the example shown in FIG.7, for each of electrodes E2, E3, and E6, the voltage is below the setvalue 60V because the output level is limited by the set temperature 95deg C. which the temperature sensor has reached. In the example shown inFIG. 7, for each of electrodes E1, E4, and E5, the voltage is limited atthe voltage set value 60V (to within the limits of control andmeasurement accuracy) because E1 is a non-temperature-sensing electrode(as indicated by the temperature sensor open-circuit indicator “--”712A) and for E4 and E5, the temperature sensor is below the set value95 deg C. Examples of non-temperature-sensing electrodes include theCosman CR “pole” needle, the Cotop CXE “pole” needle, adeep-brain-stimulation (DBS) electrode contact on which a neurosurgeonperforms an RF heat lesion before removal of the DBS electrode, anon-temperature-sensing spring-coil epidural electrode, atemperature-sensing RF electrode whose temperature sensor is broken, andother RF electrode types. Plotting of impedance and output level on thesame time axis 718 can be important for RF ablationnon-temperature-sensing electrodes, because the impedance signal givesthe physician visual feedback about boiling around the electrode activetip, which the physician wants to avoid in some cases, such as inlesioning of nervous tissue, lesioning in the brain, creating a lesionof uniform size with gas venting, and other cases. In other embodimentsof generator 700, different settings and settings values can beincluded. In some embodiments, the settings for each electrode can beset independently of other electrodes. The elapsed time readings foreach electrode, as displayed by 1:19 for electrode E1 in panel 712,indicate the same values for electrodes E1, E2, E3, and E4 because theywere energized at the same time, and a different value for each of E5and E6 because these electrode were activated by the user at a differenttimes. The graphical user interface 710 provides for simultaneous orstaggered activation of the electrode outputs, using control buttonssuch as 711.

Each electrode control button both identifies, and provides a means forchanging, the “polarity” its corresponding electrode output. In someembodiments, the generator 700 can create any pattern of connections,and sequences of connection patterns, between generator potentials andthe electrodes and ground pads. For example, some groups of electrodescan be energized in a bipolar or multipolar manner, wherein theelectrodes reciprocally carry returns currents for each other. Forexample, some electrodes can be energized in a monopolar manner, whereinone or more ground pads carries return currents from the electrodes. Inthis way, the generator can create a wide variety of heating patterns tosuit clinical needs. In some embodiments, the generator can include anautomatic controller for ground pad switching to distribute and/orcontrol current among multiple pads, such as the ground-pad switchingmethods presented in FIG. 1, FIG. 12, FIG. 14, FIG. 15, FIG. 17, FIG.19, FIG. 20, FIG. 21, FIG. 22, and FIG. 23. In some embodiments, theparameter of the ground pad current displayed to the user is the sameparameter that the ground pad switching is configured to control.

In some embodiments, the generator 700 can include a different number ofelectrode jacks and corresponding electrode-specific displays andcontrols than the number shown in FIG. 7. In some embodiments, thegenerator 700 can energize a number of electrodes selected from thelist: 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, a number more than 10. In someembodiments, the number of electrodes that can be connected to eachelectrode jack is more than one. In some embodiments, the generator 700can include a different number of ground pad jacks and correspondingground-pad current-measurement displays than the number shown in FIG. 7.In some embodiments, generator 700 can connect to, and measure currentfrom each of, a number of electrodes, wherein the number can be selectedfrom the list: 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, a number more than 10. Insome embodiments, multiple ground pads can be connected to the same jackby means of a single cable and the current flowing through each pad canbe measured by the generator 700; this can have the advantage ofsimplifying cable organization for configurations with multiple groundpads. In some embodiments, more than one ground pad can be combined intoa single ground pad structure.

In some embodiments, the generator 700 can omit the nerve stimulator. Insome embodiments, the generator 700 can be configured for tumorablation. In some embodiments, the generator 700 can be configured fornerve ablation. In some embodiments, the generator 700 can be configuredfor surgical coagulation. In some embodiments, the generator 700 can beconfigured for multiple medical applications. In some embodiments, thegenerator 700 can execute one or more of the tissue ablation methodpresented in FIG. 1, FIG. 2, FIG. 3, FIG. 4, FIG. 5, and FIG. 6. In someembodiments, the generator 700 can include one or more of the graphicaldisplays presented in FIG. 1, FIG. 2, FIG. 3, FIG. 4, FIG. 5, and FIG.6. In some embodiments, the system 700 can operate in multiple modes toaccommodate different type of electrodes and clinical objectives. Insome embodiments, generator 700 can a variety of ablation controlmethods by means of which multiple types of electrodes can becontrolled; for example, a conventional electrode, anon-temperature-sensing electrode, an internally-cooled electrodewherein a temperature sensor is positioned within the coolant flowwithin the active tip, an internally-cooled electrodes including atemperature-sensing extension tip.

In some embodiments, the ultrasound machine of system 700 can be placedin a separate chassis from the RF generator, and the ultrasound chassisand generator chassis can exchange data via a connection, such as acable. One example of a separated RF machine and ultrasound machine ispresented in FIG. 1. In some embodiments, the ultrasound machine isproduced by a first manufacturer, and the HF generator is produced by asecond manufacturer. In some embodiments, the RF generator simplydisplays ultrasound data, such as images, from a physically separate USmachine. In some embodiments, the ultrasound machine simply displaysreadings from a physically separate RF generator. In some embodiments,the transmission of data between an ultrasound machine and an RFgenerator is only in one direction. In some embodiments, thetransmission of data between an ultrasound machine and an RF generatoris only in both directions.

One advantage of a system that includes both a tissue-ablation systemand an ultrasound-imaging system is that the physician can easilycontrol both processes from the same console. One advantage of a systemthat includes both heat-lesioning and ultrasound-imaging functions isthat the physician can easily use ultrasound imaging to guide andmonitor the ablation process, such as by visualization of lesionformation relative to target structures in the body. Lesion formationcan be visualized by bubbles around the electrode tip. One advantage ofa system that includes both tissue-ablation and ultrasound-imagingfunctions is that the system can produce a single data record thatincludes an imaging record and an ablation-data record of the ablationprocess. For ablation of multiple electrodes at the same time, displayof US image data and electrode readings on the same screen has theimportant advantage of that a large amount of data can monitored by thephysician without having to turn his or her attention to a differentconsole, which could perturb the physician's handling of the ultrasoundtransducer. This is a great advantage when many outputs are controlledat the same time. This can be a great advantage when an impedance-basedcontrol method is executed for each electrode, wherein execution of themethod can produce rapid changes in electrode readings.

The application of a nerve-stimulation signal to an ablation electrodecan provide for safe and effective nerve ablation, for example, to avoidablation of a nerve which should be preserved, and to improve targetryof nerves targeted for ablation. The application of a sensory-nervestimulation signal to an ablation electrode can be used to guide theelectrode a position favorable to ablation of a target nerve, forexample a nerve carrying undesired and/or painful signals. Theapplication of a motor-nerve stimulation signal to an ablation electrodecan be used to indicate that the electrode is too close to a nervecarrying a desirable motor function, and that the motor nerve may bedamaged during ablation. Ground pad burns are an undesirablecomplication of tissue ablation, including nerve ablation. The risk ofground pad burns can increase as the generator output level increases.The risk of ground pad burns can increase as the total electrode currentoutput increases. Ground pad current is an important indicator of safeground pad usage and ground pad heating, as described in theelectrosurgical safety standard ANSI/AAMI/IEC 60601-2-2:2009. Ground padcurrent influences the current density and rate of ohmic heating oftissue is contact with the ground pad. In some embodiments, the safe useof each of multiple ground pads can be ascertained by othermeasurements, such as direct temperature measurement, voltagemeasurement, power measurement. The risk of ground pads burns canincrease with the number of electrodes energized in the same ablationsession. It can be desirable to ablate multiple nerves at the same timeto treat chronic pain. It can be desirable that a nerve ablationgenerator can perform nerve ablation using one more electrodes at thesame time, wherein the number of electrodes can be a number selectedfrom the list: 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, a number greater than 10.The use of multiple ground pads can reduce the likelihood of a groundpad burn, because electrode current is distributed to multiple groundpads. The use of independent monitoring of the current flowing througheach of multiple ground pad can reduce the likelihood a ground pad burn,because the current flowing to each pad can be monitored, for example,by the generator 700 and/or the generator user. Individual ground padcurrent monitoring can be used to detect improper ground pad placement.Individual ground pad current monitoring can be used to detect unequalcurrent distribution among multiple ground pads, such as in the casethat a first ground pad shields a second ground pad from electrodecurrent so that more electrode current flows to the first pad than thesecond pad.

An RF generator that includes a nerve stimulator, multiple ground padconnections, and individual current measurement for each ground padconnection provides three important safety features for high-current RFablation of nerves. The combination of the nerve stimulation, multipleground pads, and individual ground-pad current monitoring providesimportant safety features for multi-electrode RF ablation of nervoustissue. An RF generator that includes connections for multipleelectrodes, connections for multiple ground pads, and nerve stimulatorprovides for the safe and effective ablation of multiple nerves at thesame time. The importance of these safety features increases as thenumber of electrode increases, as the size of the electrodes increase,and as the number of cooled RF electrodes increases, because each ofthese factors can increase the total return current that ground padscarry. The use of multiple ground pads, and the use of multiple groundpads with independent current measurement and/or control, can beadvantageous for spinal nerve ablation, for example, because heatingmultiple electrodes can require more total current than the maximumcurrent rating of one typical electrosurgical ground, because heatingmultiple cooled RF electrodes can require more current than the typicalcurrent rating of an electrosurgical ground pad, because electrosurgicalground pads have a maximum current rating, and because 1 to 8 or moreelectrodes can be used in the same procedure. For example, a typicalelectrosurgical ground pad for nerve ablation conforms to theANSI/AAMI/IEC 60601-2-2:2009 standard and can be limited to carrying 700mA for 60 seconds, and heating multiple large electrodes of 18 gauge and16 gauge to a temperature in the range 80-90 deg C. can require morethan 700 mA on average over longer than 60 seconds. In the example showin FIG. 7, the total ground-pad current from six electrodes is 872 mA,distributed between two pads G1 and G2. For example, the use of multipleground pads can be important to ensure ground pad current is below themaximum value when the number of electrodes energized at the same timeis greater than four (4). One advantage of system for tissue ablationthat includes an RF generator, a nerve stimulator, two or more groundpad connections, and individual current measurement for each ground padconnection is that nerve ablation can be performed with the safety ofnerve-stimulation guidance and the safety of multiple ground pads. Thishas the important advantage of improving the efficiency, efficacy, andsafety of nerve ablation, particularly multi-electrode nerve ablation.

Referring now to FIG. 8, one embodiment of a system for HF tissueablation is presented as a block diagram in accordance with severalaspects of the present invention. In one aspect, FIG. 8 presents oneexample of a HF ablation system that includes an HF generator and animaging device in the same chassis. In one aspect, FIG. 8 presents oneexample of an RF generator that includes a nerve stimulator, multipleground pad connections, and individual current measurement for eachground pad connection. In one aspect, FIG. 8 presents one example of anRF ablation system that provides for switching of among multiple groundpads. In one aspect, FIG. 8 presents one example of an RF generatorconfigured to generate RF and stimulation signals at the same time. Inone aspect, FIG. 8 presents on example of an RF generator that providesfor connection and disconnection of each of multiple electrodes toeither an RF potential stimulation potential, reference potential, or nogenerator potential, and for sequences of these connections anddisconnections.

In some embodiments, the system in FIG. 8 can be one example of theinternal construction of the system presented in FIG. 7. In someembodiments, the system in FIG. 8 can be one example of the internalconstruction of the system presented in FIG. 9. In some embodiments, thesystem in FIG. 8 can be one example of the internal construction of thesystem presented in FIG. 10. Some embodiments of the system in FIG. 8wherein the number of electrodes and ground pads are different thanshown in FIG. 8 and wherein the ultrasound machine 808 is outside thechassis 800 can one example of the internal construction of the systempresented FIG. 1 and of the system presented in FIG. 2. In someembodiments, the ablation control methods presented in FIG. 1, FIG. 2,FIG. 3, FIG. 4, and FIG. 5 can be included in controller 840.

In FIG. 8, connection lines that cross over each other, such as atposition 801 where two wires cross each other, are not connected.Generator 800 includes controller 840 configured for measurement andautomatic control of generator output, electrode switching, ground padswitching, pump output, and user interface input; user interface 830configured for user monitoring and control of RF, stimulation, andultrasound functions; graphical display 810 of RF, stimulation, andultrasound readings and settings; ultrasound imaging device 808connected to transducer 808F; power supply 850 that includes an RFsource labeled “RF”, a nerve-stimulation source labeled “Stim”, ameasurement device MVR for the RF source, and a measurement device MVSfor the Stim source; switching unit 860 which can connect and disconnectelectrodes and ground pads from electrical potentials generated by powersupply 850; measurement unit 870 including a measurement element foreach of one or more electrodes ME1, ME2, ME3, ME4, ME5, ME6, and ameasurement element for each of one or more ground pads MG1, MG2,wherein each measurement element is configured to measure the currentand temperature (if a temperature sensor is included in the attacheddevice) of its attached electrode 861, 862, 863, 864, 865, 866 andground pad 835, 836; and connection to pump 820 for measurement andcontrol of pump functions. In some alternative embodiments, measurementunit 870 can include a single measurement element, such as ME1, that isswitched sequentially to each of multiple electrodes and/or ground pads,whereby individual current and/or temperature measurement can beperformed that is independent of the pattern and timing of connectionsof the ground pads to the generator supplies 850. In some alternativeembodiments, the current for each of N ground pads can be measured bydirectly measuring the current flowing though (N−1) of the ground pads,and subtracting the sum of those values from the total current flow fromone or more treatment electrodes to the N ground pads at the same time,by means of the principle of current conservation.

Electrodes 861, 862, 863, 864, 865, 866 are inserted into body 890.Cooled electrodes 865 and 866 are connected to coolant output of pump820. In some embodiments, each electrode 861, 862, 863, 864, 865, 866can be any type of RF electrode, including non-cooled electrode andcooled electrodes. Ground pads 835, 836 are placed on the surface ofbody 890. The graphical display 810 can be a touch screen. The graphicaldisplay 810 can be a non-touch-screen display. The graphical display candisplay measurements digitally and graphically. User interface 830 cansave RF, stimulation, and ultrasound procedure data to an internal diskand/or an external disk. Ultrasound transducer 808F can be positioned atthe surface of body 890 and configured to image the internal anatomy ofbody 890, including, for example a heat lesion within body 890. RF powersupply “RF” is configured to produce an RF signal capable of heating theelectrodes 861, 862, 863, 864, 865, 866 within body 890. Measurementelement MVR can measure the voltage, current, and power delivered by theRF source. The radiofrequency signal generator “RF” can generate asinusoidal voltage across its “+” and “−” poles, with frequency in theradiofrequency range. In some embodiments, the RF source can generate anRF signal with amplitude in the range 0-200 V-RMS. Stimulation supply“Stim” is configured to generate a nerve stimulation signal across its“+” and “−” poles, such as a waveform including biphasic square pulses.In some embodiments, stimulation source “Stim” can produce stimulationsignals to evoke sensory and motor response, such as signals thatinclude biphasic pulses with pulse-repetition rates in the range 0-200Hz, for example 50 Hz and 2 Hz. In some embodiments, the stimulationsignal generator “Stim” can produce a stimulation signal that isconfigured to block nerve conduction, such as a signal that includesbiphasic pulses in the range 1 kHz-50 kHz.

The “−” pole of each of RF and Stim sources are tied together and thiscan be the generator reference output pole/potential. The “+” pole ofthe RF output is the RF signal output pole/potential. The “−” pole ofthe RF output is the stimulation signal output pole/potential. Switchingunit 860 can connect and disconnect each of one or more electrodes tothe RF output pole, the stimulation output pole, and the referenceoutput pole. For example, electrode 861 can be connected to anddisconnected from the RF output pole, the stimulation output pole, andthe reference output pole by switches SRE1, SSE1, and SGE1,respectively. Switching unit 860 can connect and disconnect each of oneor more ground pads to the reference output pole. For example, groundpad 835 can be connected to and disconnected from the reference outputpole by switch SG1. In some embodiments, generator 800 can provide jacksthat can each be connected to either an electrode or a ground pad, andthat can be connected to any system pole. The switches in unit 860 canbe mechanical switches or other devices for changing the resistanceand/or impedance of the connection between the power supply 850 and theelectrode or ground pads jacks.

Controller 840 is connected to power supply and measurement unit 850,switching unit 860, measurement units 870, pump 820, ultrasound machine808, user interface 830, and graphical display via user interface 830.The controller 840 can execute a tissue ablation method by means ofthese connections. The controller can process measurement from the powersupply 850 and the electrode and ground pad measurements 870. Thecontroller 840 can combine measurements to produce other measurements,such as an impedance combined from the quotient of a voltage andcurrent. The controller 840 can use a measurement as input to a controlprocess. The controller 840 can display measurements and other values onthe user interface and/or graphical display. The controller 820 canenable and disable the coolant output of pump 820, adjust the outputlevel of coolant pump 820, and use signals from pump 820 as input tocontrol processes. The controller 840 can change the operation mode ofthe ultrasound machine 808. The controller 840 can adjust the ablationprocess using measurements from the ultrasound machine 808, such as anestimate of tissue temperature, an estimate of heat lesion size, anestimate of lesion size based on imaging of bubbles. The controller 840can enable and disable the output of the RF source, adjust the amplitudeof the RF source signal, and measure the RF voltage, current, and powermeasured by MVR. The controller 840 can enable and disable the Stimsource, adjust the timing of stimulation pulses, adjust the frequency ofstimulation pulses, adjust the pulse width of stimulation pulses, adjustthe amplitude of stimulation pulses, and measure the stimulation pulsevoltage and current measured by MVS. The controller 840 can operate theswitches in unit 860 and produce a sequence of switching states. Asequence of switching states can be configured for one or more of thefollowing purposes: to create a spatial pattern of heating in thetissue, to stimulate a nerve and ablate a nerve at the same time, tostimulate a nerve and ablate tissue at the same time, to regulate theground pad currents, ablate tissue, to modify nerve function, to controlthe output delivered to an electrode, to control a temperature, to suita clinical need, and other purposes. The controller 840 can energize theelectrodes in a variety of polarities and patterns thereof, including“monopolar simultaneous” or “cluster” wherein multiple electrodes arecoupled to the same HF output potential signal and referenced to one ormore ground pads; “monopolar sequential” wherein each of one or moreelectrodes is connected to an output pole at a different time, and isreferenced to one or more ground pads; “bipolar” or “dual” wherein oneor more electrodes are referenced to each one or more other electrodes;and sequential combinations of these are other polarity configurationswherein the generator automatically switches between differentpolarities. In some embodiments, the controller can automatically reduceor turn off the radiofrequency signal output from the RF supply whenconnecting and/or disconnecting an ablation electrode and/or ground padin order to avoid undesired stimulation of nerve and other excitabletissue due to transient DC signal components that can arrive fromchanging the position of a switch 860. For example, in some embodimentsincluding two ablation electrodes and one ground pad, wherein thecontroller alternately switches RF current between the two electrodes (a“bipolar” configuration), between the first electrode and the ground pad(a first “monopolar” configuration), and then the second electrode andthe ground pad (a second “monopolar” configuration), the controllerdisables the RF power supply while the switches are changing positionbetween sequential configurations. In one example operating mode, thecontroller 840 alternates the delivery of an RF and stimulation signalso that tissue, such as a nerve, is ablated at the same time as a nerveis stimulated, and so that electrical current does not flow between theRF and Stim power supplies. This can have the advantage of monitoringthe response of a nerve ablation by monitoring the stimulation responseof nerve. In some embodiments, the alternating RF and stimulationsignals can be delivered to the same electrode. In some embodiments, thealternating RF and stimulation signals can each be delivered to adifferent electrode; this can provide for ablation of a nerve at a firstposition, stimulation of the nerve at another position, and monitoringthe nerve's response to the stimulation at a third position, wherein thesecond and third positions are configured to be on opposite sides of thefirst position, and wherein the monitoring can be measurement of actionpotentials conducted by the nerve, or can be observation of a bodilyresponse produced by the nerve, such as a motor or sensory response.

In some embodiments, the system in FIG. 8 can include the pump 820within chassis 800. In some embodiments, system 800 can be connected toanother imaging device, such as an x-ray machine, fluoroscopy machine,CT scanner, MRI scanner, spiral CT scanner, intraoperative MRI scanner,OCT scanner, laparoscopic scope machine, endoscopic scope machine, videocamera. In some embodiments, another imaging device can be included inchassis 800. In some embodiments, the ultrasound machine 808 can beomitted. In some embodiments, the generator 800 can include one or moreground pad connections each with independent switching and measurement.In some embodiments, the generator 800 can include one or more electrodeconnections each with independently switching and measurement.

Referring now to FIG. 9, one embodiment of a HF system for tissueablation is presented as a schematic drawing, in accordance with severalaspects of the present invention. In one aspect, FIG. 9 presents oneexample of an integrated system for HF ablation and ultrasound imaging.FIG. 9 presents one example of an integrated system for impedance-basedpulsing control of RF ablation and ultrasound imaging for one or morecooled RF electrodes. In one aspect, FIG. 9 presents one example of anultrasound machine that controls a HF generator for tissue ablation. Inone aspect, FIG. 9 presents one example of a system for RF ablation ofnerves that includes two or more ground pad jacks, and currentmeasurement for each ground pad attached to a ground pad jack. In oneaspect, FIG. 9 presents one example of a system for HF ablation thatincludes a graph of signal output level and impedance plotted on thesame time axis for each of one or more HF electrodes.

System 900 is configured to ablate target tissue 991, 992 in living body990 by means of one or more ablation probes 961, 962; to image theliving body 990 by means of ultrasound transducer 908F; and to provide asingle-console user interface with which a physician can monitor andcontrol both the ablation process and the ultrasound imaging process.System 900 includes a bottom part 900A and a top part 900B. Bottom part900A includes an integrated peristaltic pump 926 that pumps coolant fromsupply 921 to one or more electrodes 961, 962; one or more ground-padjacks 931 configured to connect one or more ground pads 935, 936 to asystem reference potential; and one or more electrode jacks 942configured to connect one or more electrodes 961, 962 to an RF output.Top part 900B includes a base 902; upper section 904; hinge 903; one ormore ultrasound transducer jacks 908D configured to attached to one ormore ultrasound transducers 908F; ultrasound imaging controls 909; RFgenerator controls 907; display screen 910; a connection port configuredto export RF and ultrasound procedure data to USB drive 905; and aconnection port configured to export RF and ultrasound procedure data toexternal computer 906 via connection 906A, which can be a computernetwork in one example. Display screen 910 can be a touch screenmonitor. Display 910 includes ultrasound controls 913; graphic displayof ultrasound imaging data 908; RF controls 911; display 912 of digitaland graphical readings for each of the one or more electrodes 961, 962attached to the system 900; display 913 of current for each of the oneor more ground pads 935, 936 connected to the system 900; display of RFsettings values 919. The settings 919 include a set time, set power, settemperature, and mode settings. In some embodiments, the set time, settemperature, and mode settings can take values in the ranges describedin relation to settings 106A, 106C, 106D, respectively. In someembodiments, the power setting can take a value in the range 0-400 Wattsor more. In some embodiments, the power setting can be the initial powerset level. In some embodiment, the power setting can be a maximum powerset level. In some embodiments, the power setting can be the set powerlevel. Coolant from fluid bag 921 is pumped by pump head 926 throughelectrodes 961 and 962 in series and into container 925. In the examplepresented in FIG. 9, the system 900 includes two ground pad jacks 931,and six electrode jacks 942.

In some embodiments, system 900 can be an integrated ultrasound and RFsystem, wherein top 900A and bottom 900B are inseparably connected, forexample composing a single chassis. In some embodiments, top 900A andbottom 900B are physically separate and connected by a data connectionsuch as a cable, or a jack and plug. In some embodiments, bottom part900A is an RF generator that includes a coolant pump, one or more groundpad jacks, and one or more electrode jacks. In some embodiments, toppart 900B is a laptop-style ultrasound machine that includes aconnection to RF generator 900A, and user controls and displays for RFgenerator 900A. In some embodiments, the interface between RF generator900A and ultrasound machine 900B is a standardized interface that allowsone or more ultrasound system to operably connected to one or more RFgenerator, wherein the ultrasound machine and RF machine can eitherproduced by the same manufacturer, or different manufacturer. In someembodiments, generator 900A is a “black box” HF generator includingconnections for control and measure, and configured for integration intoultrasound systems.

In the operating mode shown in FIG. 9, the RF signal output delivered toeach internally-cooled electrode alternates between and high power leveland a low power level based on a measured impedance and controllerparameter. In some examples, the controller for each electrode canautomatically execute one of the methods presented in relation to FIGS.1A, 1C, 3, 4, and 5. One advantage of the system presented in FIG. 9 isthat ultrasound images and RF signal output readings are displayed onthe same screen, wherein RF signal output and cooled-RF electrodereadings can increase and decrease rapidly and repeatedly, so that thephysician can easily monitor and correlate imaging information andelectrode measurements. In some other examples, the controller for eachelectrode can execute one of the methods presented in relation to FIG.1B. In some examples, other control methods can be used.

In some embodiments, ground pad currents are not displayed to the user,but are an input to the automatic control system of the ablation system900. The automatic control system can check that the current values arewithin safety limits, prompt the user if one or more of the currentmeasures is outside allowed limits, prompt the user if the ground padcurrents are unbalanced, adjust the current flowing to one or more pads,and/or balance the current among one or more pads.

In some embodiments, system 900 can include a MW generator. In someembodiments, the one or more ablation probes 961, 962 can be MWantennae; the system 900 can include a MW generator; the one or moreground-pad jacks 931 can be omitted; and the one or more ground pads935, 936 can be omitted. In some embodiments, system 900 can omit an RFgenerator.

Referring now to FIG. 10, several embodiments of a HF system for tissueablation is presented as a schematic drawing, in accordance with severalaspects of the present invention. The text describing FIG. 10 alsopresents several methods of HF tissue ablation in accordance withseveral aspects of the present invention. In one aspect, FIG. 10presents one example of an integrated system 1000 for HF ablation andmedical imaging. In one aspect, FIG. 10 presents one example of anintegrated system 1000 for HF ablation and image-guidance for HFablation. In one aspect, FIG. 10 presents one example of a system fornerve ablation 1000 that includes a HF generator, a nerve stimulator, anerve monitor, and an ultrasound machine. In one aspect, FIG. 10presents one example of a system that can stimulate a nerve and ablate anerve at the same time. In one aspect, FIG. 10 presents one example of asystem that can stimulate a nerve while the nerve is being ablated. Inone aspect, FIG. 10 presents one example of a system that can ablate anerve and block perception of the nerve ablation by application ofelectrical signal that blocks action potential transmission to alocation between the site of nerve ablation and the central nervoussystem. In one aspect, the system 1000 has the important feature that itprovides a single console for image guidance of the placement ofstimulation, ablation, and recording electrodes at precise desiredlocations relative to one or more nerves for the purpose ofstimulation-based monitoring of a nerve ablation process.

In one embodiment, the generator 1000 in FIG. 10 can be anotheroperating mode of the generator 700 in FIG. 7. In some embodiments, theinternal circuitry of generator 1000 in FIG. 10 can be represented bythe block diagram in FIG. 8. Recording electrode 1061, RF ablationelectrode 1062, and stimulation electrode 1063 are connected togenerator jacks 1041 (“E1”), 1042 (“E2”), and 1043 (“E3”), respectively.Measurements for electrode 1061, 1062, and 1063 are displayed digitallyin panels 1011A, 1011B, and 1011C, respectively. The generator 1000 isconfigured to perform the following functions on an ongoing basis duringan ablation program: (1) record nerve signals from electrode 1061connected to jack E1; (2) deliver an RF signal to electrode 1062connected to jack E2, wherein the RF signal is configured to heat thetissue around the electrode active tip 1062C; and (3) deliver a nervestimulation signal to electrode 1063 connected to jack E3. Measurementsfor electrode 1061, 1062, 1063 are displayed graphically on plot 1018.Ultrasound data 1008 is displayed from transducer 1008E which can beused to image an electrode in relation to soft and hard tissue,including a target nerve, such as nerve 1091 in body 1090. Electrodes1061, 1062, 1063 can include ultrasound-visible features, such as aechogenic markers, configured to allow identification of eachelectrode's active tip. In the example configuration shown in FIG. 10,the active tip 1063C of stimulation electrode 1063 is placed at aproximal location along peripheral nerve 1091, which branches off spinalcord 1092. The active tip 1062C of ablation electrode 1062 is placed atlocation along peripheral nerve 1091 that is distal to the position ofstimulation electrode 1063. The measurement contact or contacts 1061C ofmeasurement electrode 1061 is placed at location along peripheral nerve1091 that is distal to the position of RF electrode 1062. Ground pad1035 carries return currents from the RF ablation electrode 1062 and thestimulation electrode 1063. In some embodiments, recording electrode1061 can be electrically referenced to ground pad 1035. In someembodiments, recording electrode 1061 can be a bipolar electrode withits own electrical reference, isolated electrically and/or temporallyfrom RF and stimulation output potentials.

The configuration of electrodes 1061, 1062, 1063 along nerve 1091 canprovide for a method of monitoring of the success or failure ofinterrupting of nerve 1091 by RF heating 1062D around RF electrode tip1062C as the nerve is being heated. When RF heating is successful at theposition of tip 1062C, the firing of nerve 1091 due to stimulation byelectrode 1063, for example by means of a sensory-nerve stimulationsignal and/or motor-nerve stimulation signal applied to electrode 1063,can be blocked by heat lesion 1062D and no longer detected by recordingelectrode 1063. The measured discontinuation of a stimulated responsecan be a condition for stopping the nerve ablation process heating. Themeasured discontinuation of a stimulated response can be a condition foraccepting the nerve ablation as complete. In one method, when the firingof nerve 1091 due to stimulation by electrode 1063 is no longerdetected, the RF ablation of nerve 1091 can be discontinued, eitherautomatically by the generator controller or by decision of the userphysician. In another method for preventing desired damage to motornerve fibers near the site of tissue ablation, a motor-nerve stimulationsignal can be delivered by output E3 through electrode 1063, a physicianand/or the generator can monitor the transmission of action potentialalong motor fibers of nerve 1091 through the position of delivery of RF(include pain-management-type pulsed RF) at tip 1062C either by means ofrecording electrode 1061 or the contraction of a muscle 1093 innervatedby nerve 1091, and the physician and/or generator can discontinue theablation process if undesired damage to motor fibers of nerve 1091 isindicated by a decrease in transmission of action potentials generatedby electrode 1063 through the site of RF application. In another methodfor preventing undesired damage to a nerve fiber, the ablation 1062D notintended to damage nerve 1091, but rather to ablate tissue nearby nerve1091, and stimulation by electrode 1063 is used to monitor undesireddamage to nerve 1091 using sensory-nerve stimulation, motor-nervestimulation, or both. In another method for monitoring the successfulablation or modulation of sensory-nerve fibers and preventing theablation of motor-nerve fiber, generator 1000 is configured to deliverthrough electrode 1063 an electrical signal configured to stimulatedboth sensory and motor nerve fibers of nerve 1091 during delivery of ahigh-frequency signal (such as an RF or pulsed RF signal) throughelectrode 1062 to nerve 1091. In some embodiments, recording electrode1061 can be placed within muscle 1093, and output E1 or generator 1000can be configured for recording the electrical activity muscle 1093evoked by stimulation by electrode 1063. In some embodiments, thelocation of electrode 1061 and the location of electrode 1063 can beswitched, so that stimulating electrode 1063 is distal to the ablationelectrode 1062 along the nerve 1091, and the recording electrode 1061 isproximal to the ablation electrode 1062 along nerve 1091. Generator 1000provides both digital and graphical displays of the stimulation,ablation, and recording processes. This can be important data for thephysician to assess the ablation process.

In another embodiment, recording electrode 1061 can be omitted, and theblockage of stimulated nerve signals can be monitored by a physiologicaland/or physical response, such as the contraction of a muscle 1093. Insome examples, nerve 1091 can be a medical branch nerve innervating amultifidus muscle 1093 in the spine. In some embodiments, the recordingelectrode 1061 can be omitted, the stimulation electrode 1063 can beplaced distal to the ablation electrode 1062 along the nerve 1091, theblockage of stimulation nerve signals can be monitored by patientperception of stimulated nerve signals; for example, this could beperformed if the electrode 1062 produces a pain-management-type pulsedRF signal with control temperature at or below 45 deg C. In someembodiments, the recording electrode 1061 can be placed proximal to theablation probe 1062 along a nerve 1091, and the stimulating electrode1063 can be placed distal to the ablation probe 1062 along a nerve 1091,and the progress of the ablation process can be monitored by changes inmeasured stimulation action potentials propagating the distal toproximal along the nerve. In some embodiments, the stimulation electrodecan be omitted, and the stimulation of action potentials can be producedby a physical and/or physiological process, such touching or moving abody part, or by an existing pain process. In some embodiments, astimulation signal and an RF ablation signal can be delivered to thesame electrode. In some embodiments, a stimulation signal and an RFablation signal can be delivered to each of one or more RF electrodes.

In another example, the configuration presented in FIG. 10 can be usedto block the patient's perception of painful sensations during nerveablation without direct application of anesthetic to the nerve. In thisexample, the recording electrode E1 can be omitted, and structure 1093can represent a painful facet joint in the spine of patient 1090 that isinnervated by medial branch nerve 1091. Generator 1000 can deliver toelectrode 1063 a stimulation signal capable of temporarily blockingsignal conduction in nerve 1091 at the same time that nerve 1091 isbeing ablated due to RF signals delivered to electrode 1062. Painsignals generated by heating at the location of active tip 1062C can beblocked by nerve-blocking stimulation signals applied by electrode 1063Cat a location proximal location along the nerve 1091. Direct applicationof anesthetic to nerve 1091 to block pain signals due to nerve heatingcan be omitted. After the ablation and stimulation signals are turnedoff, the stimulation block ceases to have an effect, and the patient canquickly assess whether painful sensations from joint 1093 were blockedby heat lesion 1062D, by contrasting pain before and after the ablation.The patient can be instructed to distinguish pre-procedure pain frompain induced due to the nerve injury. In this example, a first electrodeE3 configured to produce an electrical conduction block, is placedproximal to a second ablation E2 electrode along a sensory nerve, andoperation of the first and second electrodes reversibly blocks painsensations produced by nerve ablation at the second electrode E2 withoutthe use of anesthetic. This has the advantage that the result of anattempt at nerve ablation (namely that painful or undesired signals areblocked in the target nerve) can be evaluated immediately afterward,because direct application of anesthetic to the target nerve can beavoided without producing excessive patient discomfort. In one example,the nerve-blocking stimulation signal can be a high-frequencystimulation configured to produce a high-frequency conduction block. Inone example, nerve-blocking stimulation signal can be a biphasic signalas described in Rosenblueth A, Reboul J. The Blocking and DeblockingEffects of Alternating Currents on Nerve. Am J Physiol. 1939;125(2):251-264. High frequency alternating current with fundamentalfrequency in the range 2-50 kHz can produce a nerve block. In anotherembodiment, a nerve-blocking stimulation signal and an RF ablationsignal can be applied to the same electrode to reduce pain during RFablation. In one method, a stimulation configured to block nerve signalconduction is applied to a nerve that is being subjected to an ablationprocess, such an RF ablation process, wherein the application of thestimulation signal is configured to block the patient's sensation of theablation process.

In another example, the configuration presented in FIG. 10 can furtherinclude a fourth electrode attached to jack E4 and having an active tipthat is positioned along nerve 1091 between the active tip 1063C ofelectrode 1063 and the spinal cord 1092; generator 1000 can beconfigured to deliver a first nerve stimulation signal to jack E3configured to produce repeated nerve firing, and to deliver a secondnerve stimulation signal to jack E4 configured to block nerve signaltransmission; and the system can be one example of a system performing amethod comprising simultaneously ablating a nerve; blocking perceptionof pain from the nerve ablation by delivery of a nerve-stimulationsignal that blocks transmission to the central nervous system actionpotentials induced by the nerve ablation; and monitoring the progress ofthe nerve ablation by applying a nerve-stimulation signal configured toinduce repeated nerve firing, and either recording stimulated actionpotentials or observing a physiologic effect of stimulated actionpotentials. The said method can further comprise the step of evaluatingthe effectiveness of an action-potential-blocking nerve-stimulationsignal applied to the nerve, by applying a nerve-stimulation signal to alocation along the nerve that is distal to the location of applicationof the action-potential-blocking nerve-stimulation signal. One advantageusing an electrical signal to block perception of the nerve ablation inthis method, instead of injection of an anesthetic, is that injection ofan anesthetic can spread undesirable to the location of the applicationof the nerve-stimulation signal configured to induce repeated nervefiring, and block said firing, thereby preventing monitoring of theprogress of the nerve ablation.

In the examples presented in FIG. 10, stimulation, RF, and measurementphases of generator output and measurement can be sequenced cyclicallythroughout the ablation process so that they do not overlap in time.This has the advantage that the stimulation, RF, or measurementfunctions are not disturbed by the presence of other electrical signalsand potentials. This can be important to protect sensitive measurementcircuitry from stimulation and RF output, and to protect sensitivestimulation circuitry from high-voltage RF output. In some embodiments,the RF, stimulation, and measurement phases can be delivered at thesame. In some embodiments, the RF ablation signal is delivered by afirst electrode by a first electrical signal generator, the stimulationsignal is delivered by a second electrode by a second electrical signalgenerator, the first electrode and the second electrode are electricallyisolated except for their contact with the same patients, and the firstand second electrical signal generators are electrical isolated toprevent substantial current from flowing between the first electrode andthe second electrode. In some embodiments, the stimulation signal isgenerated by first generator unit, the RF ablation signal is generatedby a second generator unit, and the first generator unit and the secondgenerator unit are physically separate units.

Referring now to FIGS. 11, 12, 13, 14, 15, 16, 17, and 18, severalexamples of output signals produced by RF generator systems arepresented in schematic graphs as a function of time, in accordance withseveral aspects of the present invention. The horizontal axis representstime. The vertical axis represents a signal output voltage. Each signalis presented on the same time scale. Each signal is labeled on the leftby generator output jack, eg “E1” and “G1”, by which the signal isdelivered to the electrode or ground pad attached to the jack. A signallabelled “Ex” where “x” is a number is the output signal for anelectrode jack and the connected electrode. A signal labelled “Gx” where“x” is a number is the output signal for ground pad jack and theconnected ground pad. Within each signal, (such as signals 1110, 1120,and 1140 in FIG. 1), a solid line (such as lines 1111, 1123, and 1140 inFIG. 11) shows the output signal delivered to the correspondingelectrode or ground pad by the generator, for example via a closedswitch connected to a generator output pole (such as the “+” or “−” poleof the RF supply or the Stim supply in FIG. 8). Within the each signal,a dotted line (such as line 1122 in FIG. 11) indicates that the jack,and its connected electrode or ground pad, is disconnected from allgenerator output poles, for example via an open switch. A sinusoidalline, such as 1111 in FIG. 11 represents an RF signal. In someembodiments, the RF signal, such as 1111, can be generated by an RFsupply, such as the RF source of power supply 850 in FIG. 8. In someembodiments, the frequency RF signal represented by a sinusoidal line,such as 1111, is higher or lower than it appears schematically in theseschematic figures. A biphasic square pulse, such as pulse 1123 in FIG.11, represents a stimulation signal. In some embodiments, a schematicbiphasic square pulse can represent a single biphasic pulse. In someembodiments, a schematic biphasic square pulse can represent a sequenceof biphasic square pulses, such as a signal configured to produce ahigh-frequency electrical nerve block. In some embodiments, astimulation signal, such as 1123, can be generated by a stimulationsignal generator, such as the Stim source of power supply 850 in FIG. 8.A flat line, such as lines 1140 in FIG. 11, represents a constantelectrical potential. In some cases, a schematic constant electricalpotential can be the potential of the “−” output pole of RF source andStim source in power supply 850 of FIG. 8. In some embodiments, returncurrents from the electrode signals shown in each figure are carried bythe ground pads whose signals are represented in the same figure. Insome embodiments, the electrode signals can represent a measurement ofelectrical signal output other than voltage, such as current or power.In the schematic representations of signal outputs presented in thesefigures, instances in which signal output is switched from one output toanother are depicted as occurring instantaneously. In practice thesetransitions can take a non-zero time. In some embodiments, wherein thecontroller forces switching of an output signal from one electrode toanother, or from one ground pad to another, the controller candeactivate the output signal (for example by disabling the RF oscillatorof the RF power supply), then open or close one or more switches, andthen reactivate the output signal. The duration for which an outputsignal is disabled to allow for switching can be configured to cover theentire duration of the change in switch configuration. This can removesignal transients that can have an undesired and/or confoundingstimulation effect on nerves and other excitable bodily tissue. For someswitches the transition time can be a number in the range 2-30milliseconds; in other cases the switch transition time can be shorterthan 2 milliseconds or longer than 30 milliseconds. In one aspect, thepresent invention relates to a system and method wherein generatorsignal output is turned off while a switch that connects an electrode toa generator power supply is opened or closed. In one aspect, the presentinvention relates to a system and method wherein the generator signaloutput is turned off while a switch that connects a ground pad to agenerator power supply is opened or closed. In some embodiments, the RFsignal of one electrode is generated by a different RF supply than theRF supply generating the RF signal of another electrode. In theseembodiments, the controller can ensure that the two RF supplies are notactive at the same time, and/or add a time gap between the sequentialactivation of the two supplies in which neither supply is active, toavoid simulative switching transients.

Referring now to FIG. 11, one example of delivery of a nerve stimulationsignal to a first electrode while RF ablation is performed by a secondelectrode is presented in schematic graphs, in accordance with severalaspects of the present invention. In some embodiments, the signalspresented in FIG. 11 can be from a time slice of the signals deliveredto jacks E2, E3, and G1 by generator 1000 in FIG. 10. In someembodiments, the signals presented in FIG. 11 can be produced by any oneof the systems presented in FIGS. 2, 7, 8, 9, and 10.

In example of FIG. 1, signal 1110 is delivered to electrode E2 and isconfigured to generate a heat lesion around the active tip of electrodeE2. Signal 1120 is delivered to electrode E3 and is configured to astimulate a nerve in proximity to the active tip of electrode E3. Signal1140 is delivered to ground pad G1 and is a constant referencepotential. Time intervals t1, t2, t3, t4, t5, t6, t7, t8, and t9 canrepresent the periods over which the generator of signals E2, E3, and E4updates the characteristics of the signals in response to measurementparameters. For example, the amplitude of the RF ablation signal 1110 isadjusted during each time interval where it is delivered to electrodeE2. This adjustment can be configured to control the electrodetemperature, voltage, current, power, impedance, or another parameter.For example, the amplitude of the stimulation pulse 1123 and 1124changes. For example, this change can be in response to user adjustmentof the stimulation output level. The duration of the time intervals canbe configured to suit control objectives. The duration of the timeintervals can be equal or time-varying. The duration of the timeintervals can be configured to allow for temporal interleaving of RF andstimulation signals. The duration of the time intervals can beconfigured to produce a desired repetition rate for stimulation pulses.The duration of each time interval can be in less than 1 second. Theduration of each time interval can be one-third of the period of thestimulation signal 1120, wherein biphasic pulses are delivered at a ratein the range 0-50 Hz. The ground pad G1 is constantly connected to thegenerator reference potential over the time window shown in FIG. 11.When an RF signal such as 1111 is delivered to electrode E2, electrodeE3 has a high impedance to generator potentials, as shown by dotted line1122 in one example. In some embodiments, the high impedance can beproduced by opening a switch between electrode E3 and the generatorpower supply. When a stimulation signal such as 1123 is delivered toelectrode E3, electrode E2 has a high impedance to generator potentials.In some embodiments, the high impedance can be produced by opening aswitch between electrode E2 and the generator power supply. In this way,RF ablation output and stimulation output are not applied at the sametime. This has the important advantage that current does not flowbetween electrodes E1 and E2, which can damage the stimulation sourceand/or affect the desired nerve stimulation configuration. In someembodiments, a stimulation signal is applied to a first electrode, andan RF ablation signal is applied to a second electrode, at the same.

Referring now to FIG. 12, one example of the delivery of a nervestimulation signal and an RF-ablation signal to the same electrodeduring a single ablation session is presented in schematic graphs, inaccordance with several aspects of the present invention. In one aspect,FIG. 12 presents one example of simultaneous nerve ablation and nervestimulation by means of one or more electrodes. In some embodiments, thesignals presented in FIG. 12 can be from a time slice of the signalsdelivered to jacks E1, E2, E3, G1, and G4 by generator 700 in onepossible operating mode of generator 700. In some embodiments, thesignals presented in FIG. 11 can be produced by any one of the systemspresented in FIGS. 2, 7, 8, 9, and 10.

Each of the signals 1210, 1220, 1230 delivered to electrodes E1, E2, E3,respectively, includes a repeating sequence of an RF-ablation signal (eg1211), a disconnection (eg 1212), and a stimulation signal (eg 1213).Three repetitions of this sequence is shown in FIG. 12, one in each ofthe time intervals t1, t2, and t3. In some embodiments, the duration ofeach time interval can be in the range 20-1000 milliseconds. Theamplitude and duration of each RF pulse for each RF electrode can beadjusted to meet a clinical objective, such as control of temperaturefor each electrode, or for control of power, RMS current, or RMS voltageaveraged over each interval t1, t2, t3, for each electrode. In someembodiments, the duration of each time interval can be longer than 1000milliseconds. By means of this sequence, a nerve in proximity to theactive tip of each electrode is both ablated and stimulated at the sametime. In one example, the stimulation signal can be used to induce anelectrical block. In one example, the stimulation signal can be used toevoke nerve firing. The three sequences 1210, 1220, 1230 are timed sothat no output signal is delivered to more than one electrode at thesame time. This prevents current from flowing between electrodes andconfounding clinical objectives. In other embodiments, stimulation andRF-ablation signals are applied to the same electrode at the same time,or to multiple electrodes at the same time.

Return currents from each electrode E1, E2, E3 are carried by groundpads G1, G2. Ground pad G2 is constantly energized over the time windowshown in FIG. 1, as indicated by signal 1250. Ground pad G1 isintermittently disconnected from the generator potentials in periods1241 and 1242 of time intervals t2 and t3. In some embodiments, thegenerator automatically, intermittently disconnects ground pad G1 toequalize the electrical current flowing to each pad G1, G2. This is oneexample of ground-pad current control. In some embodiments, the one ormore ground pads G1, G2 are constantly connected to generator referencepotential.

The plots for electrodes E1, E2, and E3 include “dead periods” ofpositive duration in which output is not delivered to any electrode,such as period s1, s2, s3, and s4. These dead periods appear betweeneach instance where signal output switch from one electrode to another,as in the sequence where RF 1211 is delivered to electrode E1, and thenRF 1221 is applied to electrode E2, and then RF 1231 is applied toelectrode E3, and then stimulation 1213 is applied to electrode E1, andso forth. In some embodiments, the electrical supply or suppliesproducing the signal or signals being switched between electrodes(either by opening and closing a switch or switches, or by enabling anddisabling an electrical supply or supplies) are disabled for a non-zeroduration by an automatic controller to produce a dead period for thepurpose of avoiding the production of an unintended simulativetransient. In some embodiments, the electrical supply or suppliesdelivering output to an electrode are disabled to produce a dead periodof sufficient time to allow the supply or supplies to be connected ordisconnected from a ground pad, to avoid producing an unintendedsimulative transient. In some embodiments, the RF supply or suppliesproducing RF bursts 1211 and 1221 are disabled to produce dead period s1to avoid undesired switching transients when the switch connecting E1 tothe RF supply is opened and the switch connecting E2 to the RF supply isclosed. In some embodiments, the stimulation supply or suppliesproducing stimulation signals on E2 and E3 immediately before and afterdead period s2 are disabled during dead period s2 to avoid undesiredswitching transients when the switch connecting E2 to the stimulationsupply is opened and the switch connecting E3 to the stimulation supplyis closed. In some embodiments, during dead period s3, the RF supplythat is connected to electrode E3 immediately before dead period s3, andthe simulation supply that is connected to electrode E1 immediatelyafter dead period s3 are both disabled to avoid undesired switchingtransients when the switch connecting E3 to the RF supply is opened andthe switch connecting E1 to the stimulation supply is closed. In someembodiments, the power supply or supplies connected to ground pad G1 inphase 1243 are disabled during dead period s3 to avoid undesiredswitching transients when the switch connecting ground pad G1 to areference potential is opened to go from a disconnected state 1241 to aconnected state 1243. In some embodiments, the power supply or suppliesconnected to ground pad G1 in phase 1243 are disabled during dead periods4 to avoid undesired switching transients when the switch connectingground pad G1 to a reference potential is opened to go from a connectedstate 1243 to a disconnected state 1242.

Referring now to FIGS. 13, 14, 15, 16, 17, and 18, several examples ofsequences of electrode switch states for two or more electrodes arepresented in schematic diagrams, in accordance with several aspects ofthe present invention. The electrode signals presented in these figuresare examples of signals that can be generated by embodiments ofgenerators 200, 700, 800, 900, and 1000 during all or part of anablation process. In some embodiments, the switching patterns presentedare repeated throughout an ablation process. In each of the examplespresented, at least three electrodes are connected to the generator thatproduces the presented signals E1, E2, and E3. The switching patternspresented can be generalized to configurations including two or moreelectrodes. The duration of each time intervals t1, t2, t3 can be eitherthe same or different, either pre-determined or not pre-determined, andeither fixed or variable suit clinical needs. The duration of each timeinterval t1, t2, t3 can short relative to tissue responses so that thesignals' effects closely approximate the effects of a smooth signal. Insome embodiments, the RF pulse duration and amplitude of each signal canbe adjusted to meet a clinical objective such as control of temperaturefor each electrode, or for control of power, RMS current, or RMS voltageaveraged over each interval t1, t2, t3, for each electrode. In someembodiments, time periods t1, t2, and t3 can represent control-updateperiods at the end of each of which RF pulse durations, amplitudes, andorders are updated. In some embodiments, the time schedule by whichelectrodes are switched is predetermined. In some embodiments, the timeschedule by which electrodes are switched is not predetermined. In someembodiments, the time schedule by which electrodes are switched canvary, for example in response to measured parameters. In someembodiments, in accordance with one aspect of the present invention, theRF source can be disabled during switching to prevent non-zero-meanvoltage transients that can produce undesired stimulation of nerves,muscles, and other excitable tissue. This can advantageously preventundesired patient discomfort, sensations, and/or muscle contractionsduring the ablation process. Without removal of such simulativeswitching transients in multi-electrode configurations, undesiredstimulation of excitable tissue can occur in scenarios where multipleelectrodes are placed near nerves for the purpose of nerve ablation, inscenarios where multiple large cooled-RF electrodes cause high currentsto flow through the body, and in other scenarios. In one aspect of thepresent invention, disabling the RF output during switch transitions(opening and/or closing), switching transients during multi-electrodecooled-RF tumor ablation wherein the output is switched among multipleelectrodes, can prevent undesired stimulation of excitable tissue, suchas muscles, sensory nerve fibers, motor fibers. In some embodiments, thesignals can be produced by a single RF voltage source. In someembodiments, the signals can be produced by more than one RF voltagesource.

FIG. 13 presents one example of a monopolar non-concurrent switchingpattern, wherein one or more ground pads carry return currents from eachelectrode, and wherein no two electrodes are energized at the same time.FIG. 14 presents one example of a monopolar concurrent switchingpattern, wherein one or more ground pads carry return currents from eachelectrode, and wherein one or more electrode are energized at the sametime; this kind of pattern can be used to energize a cluster ofelectrode with individual control of the output to each electrode, forexample to control each electrode's temperature or impedance. FIG. 15presents one example of a monopolar concurrent pattern, wherein one ormore ground pads carry return currents from each electrode, and whereinall electrodes are energized at the same time; this kind of pattern canbe used for cluster ablation. FIG. 16 presents one example of a bipolar(or “dual”) non-concurrent switching pattern, wherein ground pads arenot used, wherein electrodes carry return current for each other, andwherein pairs of electrode are energized at different, non-overlappingtimes. In each time period t1, t2, t3, first current flows betweenelectrodes E1 and E2, then current flows between electrodes E2 and E3,and then current flows between electrodes E3 and E1. In otherembodiments of bipolar non-concurrent switching patterns, more than oneelectrode can carry return currents from one or more electrode, andorder and composition of energized groups of electrode can change. FIG.17 presents one example of a monopolar non-concurrent switching patternin which stimulation pulses are delivered at the same time as RF isdelivered. In this example, one a biphasic square stimulation pulse isadded to each burst of RF delivered to each electrode. FIG. 18 presentsone example of a monopolar concurrent switching pattern in whichstimulation pulses are delivered at the same time as RF is delivered. Inthis example, one a biphasic square stimulation pulse is added to eachburst of RF delivered to each electrode. In some embodiments, a sequenceof electrode switch states can include one or more of the patternspresented in FIGS. 13 through 18.

Referring now to FIGS. 13, 14, 15, 16, 17, and 18, several examples ofsequences of ground-pad switch states for two or more ground pads arepresented in schematic diagrams, in accordance with several aspects ofthe present invention. The ground-pads signal presented in these figuresare examples of signals that can be generated by embodiments ofgenerators 100, 200, 700, 800, 900, and 1000 during all or part of anablation process. In some embodiments, the switching patterns presentedare repeated throughout an ablation process. In each of the examplespresented, at least ground pads are connected to the generator thatproduces the presented signals G1, G2 and, in some figures, G3. Theswitching patterns presented can be generalized to configurationsincluding two or more ground pads. The duration of each time intervalst1, t2, t3 can be either the same or different, either pre-determined ornot pre-determined, and either fixed or variable suit clinical needs.The duration of each time interval t1, t2, t3 can short relative totissue responses so that the signals' effects closely approximate theeffects of a smooth signal. In some embodiments, the durations ofconnection and disconnection between each ground pad and a generatorpotential can be varied to meet a clinical objective such as control oftemperature for each ground pad, or for control of power, RMS current,or RMS voltage averaged over each interval t1, t2, t3, or over a numberof intervals, for each ground pad. In some embodiments, time periods t1,t2, and t3 can represent control-update periods at the end of each ofwhich ground-connection order and duration are updated. In someembodiments, the time schedule by which ground pads are switched ispredetermined. In some embodiments, the time schedule by which groundpads are switched is not predetermined. In some embodiments, the timeschedule by which ground pads are switched can vary, for example inresponse to measured parameters. In some embodiments, the RF source canbe turned off during switching to prevent non-zero-mean voltagetransients that can produce undesired nerve or muscle stimulation. Insome embodiments, the signals can be produced by a single RF voltagesource. In some embodiments, the signals can be produced by more thanone RF voltage source.

FIG. 13 and FIG. 18 each presents one example in which one or moreground pads are constantly connected to a generator reference potential.FIG. 16 presents one example in which one or more ground pads areconstantly disconnected from all generator potentials.

FIG. 14 and FIG. 17 each presents one example a non-concurrent switchingpattern, wherein no two ground pads are energized at the same time. Insome embodiments of non-concurrent ground pad switching patterns, theswitching time schedule is predetermined. In some embodiments ofnon-current ground pad switching patterns, the switching time scheduleis not predetermined. In some embodiments of non-current ground padswitching patterns, the switching time schedule can be variable, forexample changing in response to measured parameters during an ablationprocess.

FIG. 15 presents one example a nested-simultaneous switching patternwherein ground pads are turned off in an order, and then turned back onin the opposite order. The last ground pad to be turned off is the firstground pad to be turned back on. A given ground pad is not turned backon until all ground pads that were turned off after the given ground padhave been turned back on. In some embodiments, two or more ground padscan turn off at the same time. In some embodiments, two or more groundpads can turn on at the same time. In some embodiments ofnested-simultaneous switching, the order in which ground pads are turnedoff and on is fixed. In embodiments of nested-simultaneous ground-padswitching wherein the order in which ground pads are turned off and onis fixed, there do not exist any two time instants in the switchingsequence for which, in the first instant, a first ground pad isconnected and a second ground pad is disconnected, and, in the secondinstant, the first ground pad is disconnected and the second ground padis connected. In some embodiments of nested simultaneous switching, theorder in which the ground pads are turned off can vary across switchingcycles. For example, in one time interval the ground pads are shut offin the order G3, G2, G1, and in another time interval, the ground padsare shut off in the order G3, G1, G2. In some embodiments ofnested-simultaneous ground pad switching patterns, the switching timeschedule is predetermined. In some embodiments of nested-simultaneousground pad switching patterns, the switching time schedule is notpredetermined. In some embodiments of nested-simultaneous ground padswitching patterns, the switching time schedule can be variable, forexample changing in response to measured parameters. In some embodimentsof nested-simultaneous ground pad switching patterns, the switching timeschedule is not predetermined, but is fixed based on measuredparameters.

FIGS. 1, 2, 6, 7, 8, 9 and 10 each present examples of an ablationsystem wherein two or more ground pads can carry return currents fromone or more ablation electrodes, wherein a switch between each groundpad and a generator potential (eg the reference potential) can be openedand closed to disconnect and connect the ground pad, respectively,wherein a sequence of ground-pad switch states can be produced by anautomated controller, and wherein the current at each ground pad can bemeasured. A ground pad does not carry substantial current from anyelectrode when it is disconnected from all generator potentials, as inthe case, for example, where all switches between a ground pad andgenerator potentials are open. A ground pad can be called “active” whenit is connected to a generator potential by a closed switch or anothersubstantially low-impedance connection. A ground pad can be called“inactive” when it is disconnected from all generator potentials by anopen switch or another high-impedance connection.

Referring now to FIGS. 19, 20, 21, 22, and 23, several embodiments ofmethods for control of tissue heating by two or more ground pads arepresented as flow charts, in accordance with several aspects of thepresent invention. In one aspect, these embodiments relate to thecontrol of ground pad current by ground-pad switching. In one aspect,these embodiments relate to the control of ground pad temperature byground-pad switching. In one aspect, these embodiments relate to thecontrol of a parameter that depends on the ground-pad current byground-pad switching, examples of such a parameter include, but are notlimited to, the temperature of the ground pad, a temperature measured atthe ground pad, the current carried by the ground pad, the RMS currentcarried by the ground pad over a time period, a moving average of thecurrent carried by the ground pad, the heating power dissipated intissue near the ground pad, the impedance between the ground pad anablation electrode. In one aspect, these embodiments relate to reductionof ground-pad current. In one aspect, these embodiments relate to thereduction of ground-pad temperature. In one aspect, these embodimentsrelate to regulation of a parameter related to ground-pad current and/orground pad heating. In some embodiment, the ground pads carry RFcurrent.

Paragraph A: Given the total ablation current I produced by one or moreablation electrodes when at least one ground pad is active, a sequenceof ground-pad switch states for N ground pads, and the current flowingthrough each ground pad during the duration of the sequence, can becharacterized as follows, wherein that the total current I hasapproximately constant over the duration of the sequence. Forembodiments in which the RF current is delivered to the one or moreablation electrodes, the total current I can be the RMS value of the RFcurrent over the period of the RF carrier wave (eg 2 milliseconds for a500 kHz RF signal). The sequence has M steps, wherein for step j=1, . .. , M, the switch state can be described by indicator variable q_(ij)=1if ground pad i=1, . . . , N is active, and otherwise q_(ij)=0. Thereare 2^(N) possible switch states. Variable p_(ij) is the proportion ofthe total current I that flows to pad i during step j, and has theconstraints 0≦p_(ij)≦1 and p_(ij)+ . . . +p_(Nj)=1, for all i,j.Variable p_(ij)=0 if q_(ij)=0, and otherwise its value is affected bythe bodily system, the placement of the ablation electrode, and theplacement of it and other active ground pads in step j. The duration ofstep j is t_(j)≧0. The duty cycle for step j is d_(j)=t_(j)/t, wheret=t₁+ . . . +t_(M)+t_(S) is the total sequence duration, and wheret_(S)≧0 is optional switching time during which no electrode output isproduced. The duty cycle has constraints 0≦d_(j)≦1 and d₁+ . . .+d_(M)=1, for all j. The current flowing to pad i in step j isI_(ij)=I*p_(ij) and can have a maximum peak current constraintI_(ij)≦I_(i,max), for all i,j in some examples. The RMS current flowingthrough pad i over the total duration of the sequence isI_(i,RMS)=I*(d₁*p_(i1) ²+ . . . +d_(M)*p_(1M) ²)^(1/2) and can have amaximum RMS current constraint I_(i,RMS)≦I_(i,maxRMS) for all i. In someembodiments wherein the total current varies more generally over thesequence duration, the current flowing to pad i in step j isI_(ij)=I_(j)*p_(ij), and the RMS current flowing through pad i over thetotal duration of the sequence is I_(i,RMS)=(d₁*I₁ ²*p_(i1) ²+ . . .+d_(M)*I_(M) ²*p_(1M) ²), where I_(j) is the total RMS electrode currentis over step j. One advantage of an ablation method in which changes inthe electrode output level are synchronized to changes in the state ofground pad switches is that measurement and optimization of parametersrelated to ground pad heating can be facilitated. One importantadvantage of these equations is that they describe parameters that areimportant influences on ground pad heating. One advantage of aground-pad control system that measures the current flowing to eachground pad in two or more ground-pad switch configurations is that theseequations can be used to adjust a ground pad switching sequence tooptimize one or more parameters related to ground pad heating, withoutprior knowledge of the arrangement of the ground pads on the patientbody. For embodiments in which it is desired to control the current overtime intervals throughout an ablation process, these equations can beused for each time interval (which can be referred to as a “timewindow”) to determine a ground pad switch sequence configured to controlthe current over the time interval, including control of the maximumcurrent over the time interval, or control the average RMS current overeach time interval; examples of time intervals include a sliding timewindow, a moving time window, regular time intervals, time intervalsformed by partitioning the duration of an ablation process, timeintervals that are short relative to the thermal response of the groundpads, time intervals whose durations are less and 1 second, timeintervals whose durations are less than 5 seconds, time intervals whosedurations are less than 10 seconds, time intervals whose durations areless than 15 seconds, time intervals whose durations are less than 20seconds, time intervals whose durations are less than 30 seconds, timeinterval whose durations are greater than 30 seconds. Another advantageof a ground-pad control system that measures the current flowing to eachground pad in two or more ground-pad switch configurations is that theseequations can be used to adjust the identity of the switch states, theorder of the switch states, and/or the timing of switch states of aground pad switching sequence to program a controller to automaticallyoptimize one or more parameters that are influenced by an averagecurrent (such as an RMS current) delivered to one or more of two or moreground pads, based on measurements of the current flowing through eachground pad, without manually programming the physical arrangement of theground pads into the controller. Another advantage of a ground-padcontrol system that measures the current flowing to each ground pad intwo or more ground-pad switch configurations is that these equations canbe used in the programming of an automatic controller of a system fortissue ablation to equalize current distribution among all ground pads,using measurement of ground pad currents. In one example, by measurementof all ground-pad current portions p_(ij) for a given switching sequence{q_(ij)}, the above equations can be used by the automatic controller ofan ablation system to determine whether RMS ground-pad currents can beequalized (meaning I_(i,RMS)=I_(k,RMS) for all i,k) for some selectionof step times t₁, . . . , t_(M), and if so, then to determine the valueof the equalized RMS currents I_(i,RMS). Furthermore, these equationscan be used by a RF-generator controller to select automatically thesequence {q_(ij)}among all possible sequences that produces the smallestequalized RMS currents I_(i,RMS). One advantage of a ground-padswitching process that produces a nested-simultaneous sequence ofground-pad connections by activating all pads in the first step, anddeactivating the highest-current pad in each subsequent step until onlyone pad is active in the final step, is that the process can executed bythe automatic controller of an RF ablation system to equalize RMSground-pad currents for a variety of ground pad configurations, becauseit produces a full-rank lower-triangular matrix [I_(j) ²*p_(ij) ²] forwhich I_(RMS)=(d₁*I₁ ²*p_(i1)2+ . . . +d_(M)*I_(M) ²*p_(1M) ²)_(1/2) canbe solved for some value I_(RMS) with 0≦d_(j)≦1 and d₁+ . . . +d_(M)=1,for all j, for variety of ground pad configurations, where the groundpads have been labeled such that ground pad i is deactivated in the(i+1)-th step without loss of generality.

Referring now to FIG. 19, one embodiment of a method for control oftissue heating by two or more ground pads is presented as a flow chart,in accordance with several aspects of the present invention. In oneaspect, FIG. 19 relates to a ground-pad switching sequence configured toregulate a measured ground-pad current, wherein more than one ground padis connected to a power supply (such as a radiofrequency signalgenerator) at same time. In one aspect, FIG. 19 relates to a ground-padswitching sequence which is configured to regulate the RMS current ofeach of two or more ground pads, and in which more than one ground padis connected to an electrical signal generator at same time. In thefirst step 1900, it is confirmed that all ground pads are connected. Inone embodiment, this can be confirmed by detecting a non-zero current oneach ground pad when the electrode is conducting a current. In oneembodiment, the generator can activate only one ground pad at a time,and confirm that both the electrode and the ground pad conduct the samenon-zero current. In step 1905, an ablation program is started and thecontroller starts producing a ground-pad switching pattern, which can bea single sequence of ground pad switch states, or a sequence of repeatedground pad switch states. A switching pattern for a ground pad can beproduced by alternately opening and closing a switch that connects theground pad to the output pole of an electrical power supply. Theswitching pattern can include a time period in which only one ground padis active. The switching pattern can include a time period in which twoor more ground pads are active at the same time. The switching patterncan include a time period in which all ground pads are connected. Theswitching pattern can include a subsequence of ground-pad switch statesthat is repeated at regular time intervals, wherein in each subsequence,the duration of each configuration of ground-pad switch states isadjustable to meet an objective, such as control of a time average ofthe current flowing through a ground pad over the duration of eachsubsequence. Generally, a “time average” or “time-average” of a value isthe average of the value with respect to time over a time interval ortime intervals. The switching pattern can include a sequence of at leasttwo steps, wherein during each step, a subset (meaning “a set each ofwhose elements is an element of an inclusive set”) of the ground pads isconnected to an electrical signal generator, and ground pads notincluded in the subset, if any, are disconnected from the electricalsignal generator; and wherein subset of a first step includes at leastone element that is not contained in the subset of a second step. Theswitching pattern can include a sequence of at least two steps, whereinduring each step, a subset of the ground pads is connected to anelectrical signal generator, and the remaining ground pads are, if any,are disconnected from the electrical signal generator; and whereinground pads connected in a first step are different from the ground padsconnected in a second step. The switching pattern can include a sequenceof at least two steps, wherein during each step, the controller selectswhich ground pads are connected to a power supply and which ground padsare disconnected from the power supply; and wherein at least one of theground pads connected in a first step is not connected in a second step.Note that “all of the ground pads” is one example of“a subset of groundpads”. In step 1910, the generator can measure one or more individualground-pad currents during each of the one or more ground-pad-switchconfigurations in the pattern. In some embodiments of step 1910, thegenerator can measure one or more of the following: a ground-padtemperature, a ground-pad current, a ground-pad voltage, a ground-padpower, a measurement of tissue heating near a ground pad. In someembodiments of step 1910, the current flowing collectively to a group ofground pads can be measured. In step 1915, the generator adjusts theground-pad switching pattern. One or more aspects of the pattern can bevaried by a controller for the purpose of regulating a measured groundpad current, wherein the aspects can include the identity of the switchstates included in the pattern, the order of the switch states includedin the pattern, and the duration of each switch state included in the apattern. One or more these aspects can be predetermined. One or morethese aspects can be fixed. One or more these aspects can be determinedin response to a measurement, and then fixed afterwards. The switchingpattern can be varied to minimize the number of changes in ground-padswitch states in response to a measurement of ground pad current. Theswitching pattern can be varied to minimize the number of active groundpads. The switching patterns can be a sequential switching pattern. Theswitching pattern can be a nested-simultaneous switching pattern. Theswitching pattern can be a nested-simultaneous switching pattern whereina higher-current pad is inactivated before a lower-current pad. In someembodiments, the generator controller can include an automatic solverfor equations of Paragraph A in order to automatically regulate thecurrent flowing through each of two or more ground pads based onmeasurements of the current flowing through each of said two or moreground pads; wherein automatic solvers can be programmed usingalgebraic, closed-form, iterative, or other methods for solving tolinear and non-linear equations that are familiar to one skilled in theart of linear algebra, optimization, search, and computer algorithms.Regulating a measured ground pad current can include one or more of thefollowing: holding one or some or all ground-pad currents below a limit,holding one or some or all RMS ground-pad currents over a sliding timewindow below a limit, holding one or some or all ground-pad peakcurrents below a limit, minimizing one or some or all ground-padcurrents, minimizing one or some or all RMS ground-pad currents over amoving time window, minimizing one or some or all peak ground-padcurrents, equalizing one or some or all ground-pad currents, equalizingone or some or all RMS ground-pad currents over a moving time window,reducing the number of ground-pad switch changes, increasing the numberof active ground pads, minimizing one or some or all peak ground-padcurrents, regulating a parameter that is a influenced by a ground padcurrent, regulating a temperature for one or some or all ground pads,regulating a power for one or some or all ground pads, regulating avoltage for one or some or all ground pads, regulating the ablationelectrode output level, and regulating the current, voltage, power,output level of one or more ablation electrodes, wherein “holding belowa limit”, “minimizing”, and “equalizing” can be performed in relation toa time window, moving time window, or to the entirety of the ablationprogram. In some embodiments, the duration of the time window forregulation of a current is configured to be short relative to thetime-constant of tissue heating due to current density at or near aground pad. A “sliding” or “moving” time window can be a time windowthat at any given moment (such as the present time, or the moment atwhich a moving average is assessed), the time window includes a timesegment starting at the given moment minus the duration of the timewindow, and finishing at the given moment. An average over a moving timewindow can be referred to as a “moving average”. An RMS average over amoving time window can be referred to a “RMS moving average”, and is oneexample of a moving average. For embodiments in which the ground-padswitching pattern includes a repeated sequence of ground pad switchstates, the moving average of a parameter being controlled (such as theRMS moving average of ground pad current) by the switching pattern canbe computed over each repetition of the sequence; this is one example ofa moving average that is synchronized to the switching sequence. In step1920, if the ablation program is complete, the process terminates instep 1925, but if the ablation program is not yet complete, the processreturns to the measurement step 1910 to continue updating the switchingpattern in step 1915. The frequency with which the switching pattern isadjusted by repeated visits to step 1915 can be configured to providefor regulating a measured ground pad current. For example, the timeintervals between visits to step 1915 and adjustments of the switchpattern in each visit to step 1915 can be configured to be shortrelative to the speed of the thermal response of a ground pad whosecurrent is being regulated. For example, the time intervals betweenadjustments of the switching pattern in step 1915 can be less than 1second, less than 2 seconds, less than 5 seconds, less than 10 seconds,less than 15 seconds, less than 20 seconds, less than 30 seconds, orgreater than 30 seconds. For example, the time intervals betweenadjustments of the switching pattern in visits to step 1915 can besynchronized to the time intervals over which the average of aground-pad current (such as the RMS value of the ground-pad current) ismeasured for the purpose of regulating that average. For example, themeasurement and adjustment time intervals can be identical. For example,a whole number of the measurement time intervals make up on adjustmenttime interval.

In some embodiments of measurement step 1910, one or some or all activeground-pad currents can be measured during an exploratory switchconfiguration, and those measurements can be used to optimize theswitching sequence. For example, an exploratory switch configuration canbe brief and configured to have limited effect on regulated parameters.For example, an exploratory switch configuration can be produced duringthe down time of an ablation electrode control program, wherein thetotal current is too small to increase any ground pad temperature. Forexample, all possible switch configurations can be explored during adown time in order to perform a global optimization of the switchingsequence.

Referring now to FIG. 20, one embodiment of a method for control oftissue heating by two or more ground pads is presented as a flow chart,in accordance with several aspects of the present invention. In someembodiments, a ground-pad parameter can be one or more parametersselected from the list: temperature, current, voltage, power. Someembodiments of the method presented in FIG. 19 can be an embodiment ofthe method presented in FIG. 20. In step 2000, system can confirm thatthe ground pads are connected, for example by checking a ground-padcontact current, checking that current flows to the ground pad, orchecking that the ground pad produces a temperature measurement. In step2005, an ablation electrode produces output, for example for tissueablation, the generator controller switches return currents from theelectrode to two or more ground pads in a switching pattern. In step2010, a parameter for one or more ground pads is measured, wherein theparameter can be one or more of the items selected from the list:temperature, current, voltage, power. In step 2015, the automaticcontroller updates the switching pattern in response to one or moreground pad measurements. The updating process can include bothadjustment of timing of the switch configurations of the pattern, aswell as the switch configurations included in the pattern. In step 2020,it is checked whether the electrode ablation program is complete. If so,the ground pad switching pattern stops in Step 2025, and otherwise theprocess repeats in step 2010.

In one embodiment of the method of FIG. 20, measured ground padtemperatures are regulated in a fully automatic process that can adaptto a variety of ground pad setups, including setups that differ in thenumber of ground pads and the arrangement of ground pads on the patientbody. In this example, each ground pad includes a temperature sensor. Instep 2005, all ground pads are active. In measurement step 2010, thetemperature each ground pad is measured. In step 2015, cycle period isset, which can be a fixed value or a value that is varied in response tomeasurements. For each ground pad, the controller uses a feedbackcontroller (such as a PID controller, bang bang controller, or anotherstandard controller) to update the proportion of time during theupcoming cycle period that the ground pad is active in order to regulatethe ground pad temperature. For example, the temperature can be held ata value below a temperature capable of inducing thermal tissue damage,such as 43 deg C. In some embodiments, the controller can additionallyuse a measurement of the electrode output level (voltage, current,and/or power) as an input to the feedback controller. In someembodiments, the controller can additionally use a measurement of theground pad current as an input to the feedback controller. In someembodiments, additional measurements can be made at various timesthroughout the cycle in step 2015. The generator then generates aswitching pattern during the cycle period wherein each ground pad isconnected for the proportion of time determined by its feedbackcontroller. In one embodiment, each cycle starts with all ground padsactive, and each ground pad turns off at the time specified by itsindividual feedback controller. This forces ground pads to be active atthe same time, which advantageously reduces ground pad heating bydistributing current to multiple pads at the same time. If all groundpads reach their control value, there will be a time period in a cycleduring which no ground pad is attached and therefore no current flowsout of the ablation electrode output. This condition can be allowed topersist, or it can prompt a user warning or error condition. In someembodiments, in some cases, if the overlapping pattern will produce aperiod in which no ground pads are active, the controller can shift theactive times for the ground pads to ensure one ground pad is connectedat all time.

Referring now to FIG. 21, one embodiment of a method for limitation oftissue heating by two or more ground pads is presented as a flow chart,in accordance with several aspects of the present invention. The methodpresented in FIG. 21 can be an embodiment of the method presented inFIG. 20. The ablation process starts in step 2100. In one aspect, themethod presented in FIG. 20 is a ground-pad switching method thatincludes optimization of a switching sequence and timing that iscomputed either before a switching sequence is executed (step 2110), orwhile a switching sequence is ongoing (step 2120), or both. Computationin step 2110 can provide for global optimization of sequencesparameters. Computation in step 2120 can provide for optimization ofsequence parameters as additional, refined, or updated measurements aremade during execution of the switching sequence. In some embodiments,the measurements in step 2105 are omitted, only performed conditionally,or only performed only as needed for either step 2110 or for step 2120or for both. In some embodiments, measurements in step 2105 areperformed only once, only at the on the initial visit to step 2105, onlyintermittently, only during ablation program down times, only whenmeasured parameters differ substantially from those previously used tooptimize sequence parameters, or only when needed for subsequent updateof switching parameter in step 2110. In some embodiments, the update instep 2110 is omitted or only performed conditionally. In someembodiments, the update in step 2120 is omitted or only performedconditionally. In some embodiments, some parameters of a switch sequencecan be fixed in the first visit to step 2110, and other parameters areupdated by step 2120 throughout the ablation program. For example, insome embodiments, on the first visit to step 2110 the identity and orderof switch configurations to be included in all subsequent sequences canbe fixed, and step 2120 only determines the timing for each pre-setconfiguration. Step 215 is the start of a switching sequence of switchstates. Operations 2115, 2120, 2125, 2130, 2135, 2140, 2145, 2150, 2155,and 2160 produce the switching sequence. Each repetition of these stepsproduces another switching sequence. A switching sequence can include astep in which two or more ground pads are active at the same time. Theswitching sequence can include a step in which only one ground pad isconnected. The ground-pad currents during the switching sequence can bedescribed by the equations in Paragraph A. Step 2130 can provide for anprocess that changes switch configurations when a limit is reached, suchas, for example, when a ground pad reaches the RMS current limit for theexpected sequence duration. This can provide for minimization of thenumber of switch changes. This can provide for maximization of timespent in a desired configuration, such as a configuration in which moreground pads are active so that current is more distributed among pads.Step 2150 checks whether the sequence duration has reached its set valueat the same time as a ground pad limit was detected in step 2130. Step2155 checks whether all pads are at a limit. If not, the sequenceadvances to the next switch configuration in step 2160. If so, the allground pads are disconnected in step 2165 to prevent them from exceedingthe limit. Step 2165 will discontinue the flow of current throughablation electrodes that is configured to be carried by a ground pad,and thus reaching step 2165 can be an indication that the electrodecurrent is too high to be carried by the existing ground padconfiguration. The generator can warn the user about this situation,reduce the electrode output level, and/or discontinue the ablationprogram. In one example, step 2155 can check whether all ground padshave already carried so much current during the sequence that they wouldexceed their RMS current limit were any pad to continue being active forduring the remainder of the sequence duration. Step 2135 provides fortermination of a switching sequence based on a set value for thesequence duration. This can provide for returning to desiredconfigurations at the beginning of the sequence that were temporarilydiscontinued due to a ground pad exceeding a limit. Step 2140 canprovide for limiting the duration of a configuration to a desired value,for example, to regulate a measured value. For example, a sequence ofconfigurations and durations can be computed in step 2110 or 2120 toequalize the RMS current of all ground pads over the sequence duration.Step 2145 checks if the ablation process is complete. If the ablationprocess is complete, the process stops in Step 2170. If the ablationprocess is not complete, the ground-pad control process continues inStep 2105.

Referring now to FIG. 22, one embodiment of a method for limitation oftissue heating by two or more ground pads is presented as a flow chartin accordance with several aspects of the present invention. The methodpresented in FIG. 22 can be an embodiment of the method presented inFIG. 21 wherein the RMS current carried by each ground pad is equalizedand minimized by measurement of the current flowing through each groundpad in each of multiple switch configurations. In some embodiments, theidentity and order of the switch configurations is updated onlyintermittently, and otherwise fixed through multiple sequence cycles, ineach of which the timing of the sequence steps are updated to equalizethe RMS ground pad currents. In some embodiments, the identity and orderof the switch configurations is updated only once (for instance at aninitial time when the output level is very low, before the ablationelectrode output voltage is raised to level configured to ablate tissueat the ablation site), and otherwise fixed through multiple sequencecycles, in each of which the timing of the sequence steps are updated toequalize the RMS ground pad currents. The ablation process starts instep 2200. In the first visit to step 2205, when the electrode currentis at a low level not expected to heat any ground pad even if it is theonly active pad, the current is measured for each ground pad in all2^(N) switch configurations, where N is the number of ground pads. Insome embodiments, this step is only repeated if measured currents varysubstantially during the lesion process. In first visit to step 2210,using the data from step 2205 and equations from Paragraph A, the spaceof all configuration sequences is searched to determine the sequenceorder and timing that produces the minimum balanced distribution of RMScurrent among the ground pads over a time window. If no suchconfiguration exists because the electrode output level is too high, theelectrode current is reduced to a level that the ground pad currents cancarry. In some embodiments, the user can be notified that the number ofground pads must be increased to meet the demands of the ablationprogram. In some embodiments, because the space of all ground-padswitching sequences can be very large, the search over sequences can belimited to sequences that are likely to produce an optimal or nearoptimal balanced value, and redundant or degenerate sequences can beomitted. For example, given the four-ground-pad setup described inParagraph B, the process in step 2210 can select between the “secondnested-simultaneous switching pattern” and the “sequential switchingpattern” on the basis of the equalized ground-pad RMS current that eachpattern produces by means on the calculations described in Paragraph B.In subsequent visits to step 2210, in some embodiments, if the groundpad currents in each configuration have not changed substantially sincethe first visit to step 2210, only the timing of the sequence ofconfigurations is updated as a function of the electrode current, andthe electrode current is reduced if the ground pad RMS current capacityis exceeded. No computation is done in step 2220, only selection ofsequence parameters determined in step 2210. Steps 2230 and 2255 providea failsafe against over-current conditions due to variations in actualcurrent distribution from sequence to sequence. Step 2240 implements theswitching sequence timing in accordance with the configuration timesdetermined in step 2210. Step 2245 checks if the ablation process iscomplete. If the ablation process is complete, the process stops in Step2270. If the ablation process is not complete, the ground-pad-controlprocess continues in Step 2205.

Referring now to FIG. 23, one embodiment of a method for limitation oftissue heating by two or more ground pads is presented as a flow chart,in accordance with several aspects of the present invention. The methodpresented in FIG. 23 can be an embodiment of the method presented inFIG. 21 wherein the method is configured maximize the time in which moreground pads are active at the same time. The ablation process starts instep 2300. Step 2305 presents an example of a check on ground-pad skinadhesion wherein if a previously measured current changes substantiallyan error condition is produced. In step 2310, the sequence time is set,which in some embodiments, can be set to be fast relative to the timeconstant of ground pad heating dynamics. An RMS current limit is set foreach ground pad. In some embodiments, including for example wherein theall ground pads are identical, this can be the same value for all groundpads. No limit is placed on the time for which each switch configurationis active during the sequence; this means that each configuration timeis set to be effectively infinite so that step 2340 always follows it's“No” branch. Step 2315 starts a new ground-pad switching sequence. Inthe first visit to steps 2320 and 2325 in each sequence, all ground padsare connected. This configuration is maintained by steps 2330, 2335, and2340 until either (1) the RMS current for a ground pad over the entiretyof the switching sequence time (including both the time that has alreadyelapsed during the present sequence and any future remaining time forthe present sequence) is presently equal to its RMS current limit andwill exceed that limit if any additional current is delivery to thatground pad during the remaining sequence time, or (2) the sequence timehas elapsed. In case (2), step 2305 follows step 2335, the presentswitching sequence ends, and the next switching sequence begins. If case(1), step 2350 follows step 2330. Step 2350 proceeds to the nextswitching sequence if the present sequence time has elapsed. Step 2355checks whether all ground pads must be deactivated. If so, all groundpads are held inactive in step 2365 until the sequence time has elapsedto prevent an over-RMS-current condition on some or all pads. If not,the sequence advances to the second switch configuration, for whichsteps 2320 and 2325 turn off the ground pad(s) that reached their RMScurrent limits during the first switch-configuration period, and thecycle will repeat. In each successive cycle wherein one or more groundpads reach the RMS current limit, the number of active ground pads isdecreased. This continues until the sequence time elapses (step 2335 or2350) or all ground pads are inactivated (steps 2355 and 2365), afterwhich the next sequence begins with all ground pads active. By thismethod, during each sequence period, no ground pad substantially exceedsits RMS current limit. The method gives preference is given to groundpad switch configurations with more active ground pads. This canadvantageously reduce the RMS ground pad currents by distributingcurrent across multiple ground pads at the same time (even in caseswherein the distribution of currents is small due to the arrangement ofground pads, such as in the case where ground pads are placed along thelength of a limb). In some embodiments of the method in FIG. 23, thecontroller can be configured to fix the i-th switch configuration afterthe first time it is set; in that case, this method will produce anested-simultaneous sequence throughout the ablation process. In someembodiments, of the method in FIG. 23, the controller can compute theconfiguration time the i-th configuration in step 2320 based onpreviously measured distribution of ground-pad currents for the i-thconfiguration (such as, for example, by using equations of Paragraph A),and then use the configuration time as a limit in step 2340. Step 2345checks if the ablation process is complete. If the ablation process iscomplete, the process stops in Step 2370. If the ablation process is notcomplete, the ground-pad-control-process continues in Step 2305.

Referring now to FIGS. 19, 20, 21, 22, and 23, in some embodiments, acheck for completion of the ablation program (eg 2145, 2245, or 2345)can be inserted at any location in the flow chart. In some embodiments,a check for ground pad connection and skin adhesion (for instance byobservation of a change in the proportions of current distribution for agiven switch configuration) can be inserted at any location in the flowchart. In some embodiments, a check for ground pad connection and skinadhesion can be omitted. In some embodiments, a controller implementingthe ground pad switching method can access and use the state of theelectrode output and/or the ablation-control controller.

Referring now to FIG. 24, one embodiment of a method for HF tissueablation is presented as a flow chart, in accordance with severalaspects of the present invention. In one aspect, this method relates tothe control of a HF ablation process using an internally-cooled HFelectrode by means of an automated controller, graphic display of HFsignal output parameters, and ultrasound imaging. In some embodiments,the FIG. 24 is a method for control of a HF ablation process using aninternally-cooled HF electrode, an automated controller, ultrasoundimaging comprising viewing the controlling both the ablation processparameters and ultrasound images of the ablation site on same controlconsole. In some embodiments, the method can be performed using any oneof the systems presented in FIGS. 1, 2, 6, 7, 8, 9, and 10. The methodstarts in step 2404 wherein an internally-cooled HF electrode isselected. The type and/or the size of the electrode can be selected. Theelectrode can be one of the following: In some embodiments, ablationprobes 150, 150A, 150B, 150C, 160, can each be any one ore thefollowing: cooled RF electrode, a cooled RF electrode inside an RFcannula, a cooled RF electrode with extension-tip temperature sensor,cooled RF electrode with lateral temperature sensor, cooled RF electrodetemperature sensory on outer surface proximal to the active tip,perfusion RF electrode, cool-wet RF electrode, single-prong cooled RFelectrode, multi-prong cooled RF electrode, cooled cluster RF electrode,a cooled RF cluster electrode with two electrode shafts, a cooled RFcluster electrode with three electrode shafts, a cooled RF clusterelectrode with four electrode shafts, a cooled RF cluster electrode morethan four electrode shafts, multiple RF electrodes of any of theaforementioned types, cooled MW ablation antenna, multiple cooled MWablation antennae, a cluster MW antenna, and other type of HF ablationprobes. Selectable parameters of the size of the electrode can includethe active tip length, the active tip diameter, the prong geometry, thenumber of prongs, and other geometric and dimensional parameters. Theelectrode size can be selected as a function of one or more of thefollowing parameters and data: the size of the target tissue volume, thesize of a target tumor, the target tissue type, the type of a targettumor, the type of tissue surrounding or nearby a target tumor, imagingdata of the target tissue, ultrasound imaging of the target tissue,intraoperative imaging data, preoperative image data. The electrode canbe selected by the physician to fulfill a clinical objective. A computersystem included in a HF generator can automatically recommend and/orselect the electrode based on measured on provided parameters and/ormeasured data. For an RF electrode, one or more reference ground padsare applied to the patient skin to carry return current from theelectrode. The number and type of ground pad(s) can be selected based onthe electrode type, electrode size, target tissue characteristic,maximum expected generator output level, desired heat lesion size, andother parameters. In step 2408, the electrode is connected to the HFgenerator configured to deliver a HF electrical signal to the electrode,such as an RF generator or a MW generator. The electrode is connected toa coolant source, such a peristaltic pump delivering a fluid or acryogenic coolant source. If present, the ground pads can be connectedto the generator reference jacks. In step 2412, an ultrasound imagingapparatus is applied to the patient body and configured to image thetarget tissue in relation to the HF electrode. In step 2416, parametersof the controller for the computer graphic display of the generator andgenerator signal output are set. Some or all of these parameters can beset by the physician. Some or all of these parameters can be set by thegenerator controller based on one or more of the following:measurements, input provided by the physician, imaging data, ultrasoundimaging data, the electrode type, the electrode size, the target tissuesize, target tissue type, target tumor size, target tumor type, tissuetype nearby the target tumor, the desired treatment time, the number ofground pads, ground pad characteristics, clinical objectives, and otherfactors. The computer graphic display can be adjusted depending on anyor all of the aforementioned measurements, factors, and data, includingthe electrode type and size. The computer graphic display can displayablation parameters digitally and graphically, including parameters ofthe HF signal output, parameters of the electrode such as temperatureand current, parameters of the ground pads such as temperature andcurrent. Graphical display of the appropriate parameters can be animportant factor for safe, effective, and efficient HF ablation. Oneadvantage of graphical display of parameters in the form of a graph overtime is that the physician can easily and quickly observe the stabilityor instability of the ablation process, error conditions that aretransient or persistent, and other parameters of the ablation process.In one example, graphical display is important for monitoring of anablation process that includes tissue boiling. In step 2420, theablation process is initiated and HF signal output from the generator isdelivered to the tissue by the electrode. In step 2422, the generatoradjusts the electrode signal output to stabilize the ablation process.For this purpose, the generator can measure and/or regulate one or moreof the following: electrode voltage, electrode current, electrode power,electrode temperature, electrode polarity, multi-electrode switchingpattern, temperature probe measurement, ultrasound image data,measurements of heat lesion size, ultrasound image of bubble zone,ultrasound-derived temperature measurements. In step 2422, for an RFgenerator and electrode with two or more ground pads, the generator canadjust the ground pad configuration to regulate and/or limit ground-padheating and/or fulfill another clinical objective. In some embodiments,the generator can open and close switches that connect each ground padto the ground reference potential in a pattern over time that isconfigured to regulate the average current distribution among the groundpads, regulate measured ground pad temperatures, and/or reduce groundpad heating. In some embodiments, the generator can adjust a variableresistor in series with each ground pad to regulate current distributionacross ground pads. In step 2424, the generator displays parameters ofthe generator signal output on the computer graphic display of thegenerator. Graphical plots of ablation parameters and ground padparameters can be displayed over time to provide the physician withclear and rapidly understandable information about the ablation process.The graphical display can show rapid changes in the generator operatingmode in response to measured parameters, such as transitions betweenup-time and down-times due to impedance spikes during a cooled HFablation process. The graphical display can show intermittentirregularities in electrode and ground pad parameters that can be viewedand interpreted after they occur. The graphical history of such displaysprovides important context to the present and ongoing measuredthroughout the ablation process. In step 2428, ultrasound imaging datais presented to the physician to monitor the ablation process. Forexample, the physician can monitor the development of a bubble zonearound a HF electrode, and observe its variations and their correlationto signal output variations. In some embodiments, the ultrasound datacan influence the ablation process either by a manual process or anautomatic process. For example, the physician can adjust controllerparameters in response to measured ultrasound data. For example, thecontroller can automatically process ultrasound data by image processingtechniques to assess lesion size, the rate of lesion size growth,maximum temperatures. For automated feedback, it is advantageous to havean ultrasound image either from a fixed location relative to anatomy, orregistered to patient anatomy by a transducer position and orientationtracking system. The ablation monitoring and control process 2422, 2424,2428 can repeat throughout the ablation process, until in step 2432, theHF output signal is shut off when the ablation process has operated fora desired amount of time. In some embodiments, the ablation time can bea preset value, for example based on the electrode type, a clinicalobjective, target tissue characteristics, desired lesion size, and otherfactors before the ablation process was started. In some embodiments,the ablation time can be determined by measurement of the progress ofthe ablation process, for example based on measurement of lesions size,measurements of HF signal parameters, timing parameters of the ablationcontrol process, total delivered energy, the degree of decline indelivery energy during the ablation process, a measured temperature, atissue temperature at a location distant from the electrode, and otherparameters. In some embodiments, the ablation control processes of steps2420, 2422, 2424, and 2428 can include one or more of the methods forcontrol of HF ablation presented in FIGS. 3, 4, 5, 11, 12, 13, 14, 15,16, 17, 18, 19, 20, 21, 22, and 23.

Referring now to FIG. 25, one embodiment of a guideblock 2500 foralignment of two or more ablation probes within a body is presented as aschematic diagram showing three perpendicular external views of theguideblock, in accordance with several aspects of the present invention.The guideblock 2500 is shown in a bottom view labeled “Bottom View”, afirst side view labeled “Side View 1”, and a second view “Side View 2”.The guideblock 2500 includes thirteen guideholes, such as 2501, 2502,2503, 2504, and 2505, which are mutually parallel, and each of whichgoes completely through the top-to-bottom thickness T of the guideblockand is configured to allow passage of an elongated HF ablation probe,such as an RF electrode or cannula, through the guideblock thickness Twith sufficiently close clearance (for example, in the range 0.001-0.004inches) to hold parallel multiple probes each passing through one ofmultiple guideholes as the probes are inserted into a body (for example190 in FIG. 1) for the purpose of tissue ablation. In some embodiments,the guidehole diameter is increased to increase the clearance betweenthe ablation probe and the guidehole (for example, greater than 0.004inches) to allow the physician more flexibility in orienting andpositioning the ablation probe, so that the position of the ablation isless restricted by the block 2500; in these embodiments, the ablationprobes are inserted in a non-predetermined configuration. In FIG. 25,each guidehole (eg 2501) is configured to admit and align a 15-gaugeablation probe shaft. In other embodiments, each guideholes (eg 2501)can be sized to admit and align probes with a shaft diameter selectedfrom the range 23 to 10 gauge. In FIG. 25, the thickness T is 15 mm. Inother embodiments, the thickness T of the guideblock can be in the range1 to 30 mm or more. In other embodiments, a lesser thickness T can beused to reduce guideblock size, to allow for deeper probe penetration intissue, and/or to allow for more physician flexibility in orientingablation probes passing through the guideholes (eg 2501) since a thinnerblock can be less restrictive of probe orientation and probes can beinserted in a non-predetermined configuration. A physician may desiremore flexibility in probe orientation to suit clinical needs, target avariety of anatomical structures with the ablation probes, to shape orextend the lesion zone or zone, and/or to avoid anatomical hindrancesthrough which ablation probe should not or cannot pass, such as delicatestructures or hard structures like the ribs. In other embodiments, thethickness T can be increased to more constrain the orientation ofablation probes. All of the guideholes are shown in the Bottom View.Only the guideholes 2501, 2502, 2503 are shown in Side View 1, eachthrough hole shown as a pair of parallel dashed lines going through thethickness T of the block 2500. Only the guideholes 2502, 2503, 2504 areshown in Side View 2, each through hole shown as a pair of paralleldashed lines going through the thickness T of the block 2500; one of thedashed lines for hole 2504 overlapping the solid line of another featureof the guideblock 2500. The guideblock 2500 provides for alignment ofbetween two and thirteen (inclusive) ablation probes and/or satellitetemperature sensors in a variety of parallel-probe configurations. Forexample, three ablation probes can be inserted through holes 2501, 2502,2503 (one probe in each hole) to produce a parallel,equilateral-triangle configuration, wherein the inter-electrode spacingis 20 mm. For example, three ablation probes can be inserted throughholes 2501, 2502, 2505 (one probe in each hole) to produce a parallel,isosceles-triangle configuration. Block 2500 provides for placement ofthree ablation probes in a parallel, equilateral-triangle configurationhaving electrode spacing of either 5, 10, 15, or 20 mm. Block 2500provides for placement of three ablation probes in equilateral,isosceles, or arbitrary triangular configurations. Block 2500 providesfor placement of two to four ablation probes in a parallel-shaft, lineararrangement. Block 2500 provides for placement of a first probe in thecentral hole 2504, and one or more ablation probes arrayed around thefirst probe, for example in holes 2501, 2502, 2503. Block 2500 canprovide for placement of an ablation probe in the central hole 2504, andone or more satellite temperature probes arrayed around the ablationprobe at a variety of distances to monitor and/or control the growth ofan ablation zone produced by the ablation probe. Block 2500 has theadvantage that multiple electrodes can be constrained in a parallelconfiguration with known spacing in the body to produce a singleenlarged heating zone by energizing multiple probes at the same time.Block 2500 has the advantage of allowing the physician to move anablation probe between nearby holes (separated by 2-3 mm) to make fineadjustments to the geometry of the ablation zone or to avoid anatomicalstructures blocking placement of an ablation probe from a desired bodilylocation. Block 2500 has the advantage that multiple electrodes can beinserted in a geometric arrangement to create multiple separate lesionsin a desired arrangement, for example by inserting electrodes into moredistant guide holes, or by inserting electrodes to different depths. Theguideblock 2500 further includes fiducial markers 2531, 2532, 2533inserted into the bottom surface of the block 2500, having a knowngeometric arrangement, and visible in at least one medical imaging type(such as CT, MRI, PET, x-ray, and/or fluoroscopy). The markers 2531,2532, 2533 are arranged in a triangle for which no two sides have thesame length, so that when the markers are imaged in three-dimensions(such as by CT, MRI, or PET) the location and orientation of the block2500 can be unambiguously determined in relation to patient anatomy, andthe known geometry of the block 2500 and ablation probe can be used toplan ablation probe placement in patient anatomy. In some embodiments ofblock 2500, additional fiducial markers can be included throughout theblock to improve localization accuracy and robustness. The fiducials2531, 2532, 2533 are visible in the Bottom View. The fiducials 2531,2532, 2533 are shown as dotted line within the block 2500 in the SideView 1. Only fiducials 2532 and 2533 are shown as dotted line within theblock 2500 in the Side View 2. In planes parallel to the bottom of theblock 2500, the guideblock cross-section has three branches 2541, 2542,2543, each containing several guideholes. The guideblock 2500 includesthin walls around each of the guideholes. This guideblock geometry hasthe advantage that an ultrasound transducer can be brought close to eachablation probe during insertion, and the orientation of the ultrasoundtransducer can be adjusted by the physician within minimal interferencefrom the block 2500 in order to improve surgical guidance; this is anadvantage of use of guideblock 2500 with the electrosurgical systemspresented in relation to FIGS. 1, 2, 6, 7, 8, 9 and 10. In one aspect,the guideblock 2500 is directed toward the problem of aligning multipleablation probes in a body using ultrasound guidance, providing for clearultrasound views during placement of the ablation probes, and allowingfor fine adjustment of ablation probe spacing to adapt to anatomicalconstraints and clinical objectives during an ablation procedure. In oneaspect, the guideblock 2500 is directed toward the problem of aligningmultiple ablation probes in a body in a non-predetermined configurationusing ultrasound guidance, providing for clear ultrasound views duringplacement of the ablation probes, and allowing for fine adjustment ofablation probe spacing to adapt to anatomical constraints and clinicalobjectives during an ablation procedure. In some embodiments, eachguideholes can have one of a variety of sizes within block 2500 so thateach hole is specialized to admit one of a variety of probe types, suchas thinner guide needles, ablation probes of different types, andsatellite temperature probes. In some embodiments, the guideblock 2500cross-section can have a different number of branches, such as numberselected from the list 4, 5, 6, 7, 8. For example, a four-branchguideblock can be used to produce square or rectangular probeconfigurations. In some embodiments, the guideblock 2500 can includenon-parallel holes. In some embodiments, the guideholes of block 2500can be arranged with different spacings, for example, to provide for anequilateral triangular configuration with 12 mm inter-probe spacing. Inalternative embodiments, the guideholes of block 2500 can include sideopenings that provide for removal of the guideblock from the ablationprobes the ablation probes are inserted into the body. For example, inone embodiment, each guidehole except the central hole 2504 can be acurved slot following a circular path, wherein the circle is centered atthe center of central hole 2504, and the circle is parallel to thebottom surface of the block 2500; in this example, after three probesare inserted into bodily tissue through three holes each on a differentbranch of the alternative block, the alternative block 2500 can berotated around the central axis of the central hole 2504, one end of thealternative block 2500 can be lifted up, and the block 2500 removed bylateral movement between the probes, providing that the block thicknessT is less than the inter-probe spacing. In some embodiments, theguideblock 2500 can be adapted to allow for its removal from ablationprobes having hubs and having been inserted through the block 2500 andinto bodily tissue, without removing the probes from the bodily tissue,by building the block 2500 with multiple parts that can be broken apartthereby opening the guideholes of the block.

In some alternative embodiments, the guideblock 2500 can have acylindrical shape with guidehole therethrough (similar to the block 157in FIG. 1C), having a circular cross-section, rather than a branchedcross-section as shown in FIG. 25. In some alternative embodiments, theguideblock 2500 can have a different shape, including one of thefollowing selected from the list: cylindrical, rectangular volume,cubic, ellipsoidal cylinder, and solid with triangular cross-section anduniform thickness. In some embodiments, the central hole 2504 can beomitted from block 2500. In some embodiments, different arrangements ofholes can be included in block 2500.

Referring now to FIG. 26, one embodiment of a set of guideblocks 2605,2610, 2615, 2620 is presented as a schematic diagram in an external viewfrom the top of the guideblocks, in accordance with several aspects ofthe present invention. Each guideblock 2605, 2610, 2615, 2620 hassimilar construction and side views as the block 2500 in FIG. 25. Eachblock 2605, 2610, 2615, 2620 includes a central guide-needle hole (forexample 2624 in block 2620) through the top-to-bottom thickness of theblock, and three, equally-spaced, parallel, ablation-probe guideholesthrough the top-to-bottom block thickness (for example 2622 in block2620), each guidehole being positioned at the distal end of a branch ofthe block cross-section. The central guide-needle hole can be used toprovisionally align the guideblock in anatomy using a guide-needle thatis thinner than the ablation probe, such as a 28-20 gauge needle. Block2605 can used to align three ablation probes in a body, in parallel, andin an equilateral triangular configuration with 5 mm probe spacing.Block 2610 can used to align three ablation probes in a body, inparallel, and in an equilateral triangular configuration with 10 mmprobe spacing. Block 2615 can used to align three ablation probes in abody, in parallel, and in an equilateral triangular configuration with15 mm probe spacing. Block 2620 can used to align three ablation probesin a body, in parallel, and in an equilateral triangular configurationwith 20 mm probe spacing. In some embodiments, the set of guideblockscan include guideblocks that provide for equilateral triangularconfiguration with different spacings, for example as spacing in therange 5-30 mm or more. In some embodiments, the set can includeguideblocks that provide for other triangular, rectangular, and/ornon-parallel electrode configurations. The set of guideblocks 2605,2610, 2615, 2620 allows a physician to adapt inter-electrode spacingduring the procedure to suit clinical needs and to conform to anatomicalconstraints, and at the same time, use a guideblock that has minimalmaterial around the desired guideholes to allow for minimal obstructionof the insertion site by the guideblock. This can be important whenusing ultrasound to guide ablation probe insertion (for example, asshown in FIGS. 1, 2, 6, 7, 8, 9 and 10) because probe-placement can befacilitated and improve by bringing the ultrasound transducer close tothe point of insertion of the probe into the patient skin surface in apercutaneous procedure, or into the organ surface in an open surgicalprocedure, and by adjusting the orientation and position of theultrasound transducer around the ablation probe to view a variety ofanatomical structures in a variety of planes around the ablation probeshaft and active tip. In one aspect, the set of guideblocks 2605, 2610,2615, 2620 is directed toward the problem of aligning multiple ablationprobes in a body using ultrasound guidance, providing for clearultrasound views during placement of the ablation probes, and allowingfor adjustment of ablation probe spacing to adapt to anatomicalconstraints and clinical objectives. The set of guideblocks 2605, 2610,2615, 2620 can be provided in a single sterile package, or in separatesterile packages, or can be autoclavable. In some embodiments, thecross-sectional area of the portion of the guideblock branches that aremore central to the guideholes can be reduced to further reduce theguideblock size. In some embodiments, each of the guideblocks 2605,2610, 2615, 2620 can include fiducial markers for localization of eachblock in a medical image and surgical planning. In some embodiments,each guideblock in a set can include a unique arrangement of fiducialmarkers so that each guideblock can be identified in a medical imagewithout prior knowledge of which guideblock appears in the image. Insome embodiments, the guide holes (eg 2622) can have loose clearancerelative to the ablation probes and the ablation probes can be insertedin a non-predetermined configuration.

Referring now to FIG. 27, one embodiment of a pair of stackableguideblocks 2700, 2760 is presented in several schematic diagrams, inaccordance with several aspects of the present invention. FIG. 27 referscollectively to FIG. 27A, FIG. 27B, and FIG. 27C. Guideblocks 2700 and2760 are identical. In FIG. 27A, block 2700 is shown in towperpendicular external views, a view of the block's bottom labeled“Bottom View”, and a view of one side of the block labeled “Side View”.Like block 2500, block 2700 has thirteen guideholes (such as 2701, 2702and 2703) that pass clear through the thickness of the guideblock fromtop to bottom. All guideholes of block 2700 are shown in the BottomView, but only holes 2701, 2702, 2703 are shown through the side wallsof the block 2700 as dashed lines in the Size View of FIG. 27A. Theguideblock 2700 has a maximum top-to-bottom thickness of 3 mm. In someembodiments, the thickness of block 2700 can be in the range 1-10 mm.The block 2700 includes an interlock feature 2710 on its top surfacethat is complementary to the interlock feature 2711 on its bottomsurface. In the Side View of FIG. 1A, the recessed interlock area 2711is shown through the side walls of the block 2700 as dotted lines 2711.The interlock prominence 2710 and interlock recessed area 2711 are sizedso that the top of an identical copy of block 2700 (such as block 2760)can fit into the bottom of block 2700 with an interference fit, and sothat the bottom of an identical copy of block 2700 (such as block 2760)can fit over the top of block 2700 with an interference fit. Theinterference fits are configured such that when two blocks, such as 2700and 2760, are interlocked as shown in FIG. 27B in an external side view,the blocks will not separate or rotate relative to each other unlessthey are manipulated. In FIG. 27B, the interlock tab 2770 on the top ofblock 2760 is shown through the side wall of block 2700 as a dottedline, and the tab 2770 fits into the interlock slot 2711 on the bottomof block 2700, the slot 2711 being shown as a dashed line through theside wall of block 2700. One advantage of interlocking guideblocks 2700and 2760 is that they can be moved as a single piece along the shafts ofablation probes. One advantage of interlocking guideblocks 2700 and 2760is that the combined guideblock thickness T1, shown in FIG. 27B, can besmall to produce minimal obstruction of the surgical site, particularlywhen using ultrasound guidance. The block 2700 further includes releasetab 2740, and block 2760 further includes release tab 2741, so that whenthe blocks 2700 and 2760 are interlocked as shown in FIG. 27B, aphysician can easily separate the blocks 2700, 2760 by manipulation ofthe release tabs 2740, 2741 even when the physician is wearing sterileplastic gloves. In some embodiments, the interlock and releasemechanisms can take other forms, such as a latch, clip, pin into hole,or other forms of mechanical interlock and release mechanisms. In someembodiments, the interlock features can only loosely engage the twoblocks 2700, 2760 to help prevent rotational misalignment of the blocks,but not hold the blocks together; an advantage of this configuration isthat the blocks can be more easily and quickly moved relatively to eachother. In some embodiments of block 2700, the interlock features 2710and 2711 can be omitted. In some embodiments of block 2700, themanipulation tab 2740 can be omitted. In some embodiments, themanipulation tab 2740 can take other forms or be included inmultiplicity, for example on each branch of the block 2700.

Referring now to FIG. 27C, three RF cannula 2751, 2752, 2753 areinserted through guideblocks 2700 and 2760, through the skin surface2798 of a body containing a tumor 2791. The RF cannula 2751, 2752, 2753can each be configured to be used with an internally-cooled RF electrode(such as shown, in one embodiment, in relation to ablation probe 150 inFIG. 1A) or a non-cooled RF electrode. Cannula 2751 includes female luerhub 1751H, a cylindrical stainless steel hypotube shaft covered by athin layer of electrical insulation in proximal region 27511 and havingmetallic active tip 2751 IT at it distal end, and a removable styletincluding hub cap 2751C and solid stylet shaft inserted into the innerlumen of the hypotube shaft and having a distal sharp bevel point thatis match ground to the distal bevel point of the hypotube shaft. Cannula2752 includes female luer hub 1752H, a cylindrical stainless steelhypotube shaft covered by a thin layer of electrical insulation inproximal region 2752I and having metallic active tip 2752T at it distalend, and a removable stylet including hub cap 2752C and solid styletshaft inserted into the inner lumen of the hypotube shaft and having adistal bevel point match ground to the distal sharp bevel point of thehypotube shaft. Cannula 2753 includes female luer hub 1753H, acylindrical stainless steel hypotube shaft covered by a thin layer ofinsulation in proximal region 2753I and having metallic active tip 2753Tat it distal end, and a removable stylet including hub cap 2753C andsolid stylet shaft 2753S inserted into the inner lumen of the hypotubeshaft and having a distal bevel point match ground to the distal sharpbevel point of the hypotube shaft. The stylet shaft 2753S is shownwithin the lumen of the cannula hypotube shaft 2753I, 2753T as a dottedline. The luer port stem 2753P of hub 2753H is shown within cap 2753C asa dotted line. Cannula 2751, 2752, 2753 are inserted through holes 2701,2702, 2703 of guideblock 2700, and through the corresponding holes ofguideblock 2760, respectively, thereby forming a parallel-shaft,equilateral-triangle probe configuration having an inter-probe spacingof 15 mm. Cannula 2751 and 2752 are positioned in the tumor 2798, andthe guideblocks 2700 and 2760 are separated to produce an effectiveguideblock thickness T2, which is much larger than the thickness of theindividual guideblocks 2700, 2760, and much larger than the thickness T1of the combination of the guideblocks shown in FIG. 27B. The largeeffective guideblock thickness T2 constrains the orientation of ablationcannula 2753, and thus keeps cannula 2753 parallel to probes 2751 and2752, as cannula 2753 is inserted into tumor 2798 which resides at adepth in tissue below the skin surface 2791. In some embodiments, thetarget structure 2798 can be an anatomical structure other than a tumor,such as a nerve, an osteoid osteoma, a blood vessel, the interior of avertebra into which bone cement will be injected, or a region of tissuein which it is desired to coagulate blood flow. In some embodiments, thecannulae 2751, 2752, 2753 can be inserted to different depths relativeto skin 2798, block 2700, or block 2760, for example as in the stateshown in FIG. 27C; thereby a single lesion volume can be created with anirregular shape, separate lesion volumes can be created, andnon-predetermined cannula configurations can be created.

Referring to FIG. 27, one advantage of the stackable guideblock pair2700, 2760 is that, during an ablation procedure, a physician can reducethe combined thickness of the pair (for example, to thickness T1) toreduce obstruction at the surgical site, to allow an ultrasoundtransducer to be brought close to ablation probes aligned by the block,to allow an ultrasound transducer to be manipulated around ablationprobes aligned by the blocks, to allow more length of the probe shaftsto be inserted to the body, and to less restrict the orientation theprobes 2751, 2752, 2753 passing through the guideholes thereby allowinga physician more flexibility in placing the probes through theguideblocks; and a physician can also increase the combined thickness ofthe guideblock pair (for example to thickness T2) to increasinglyconstrain the relative orientation of multiple ablation probes as theyare inserted into a body. The interlock and release features of blocks2700 and 2760 provide an important ergonomic advantage for the use ofthe stackable guideblocks, particularly when using ultrasound guidance,because the physician generally has one hand occupied by holding theultrasound transducer. The use electrode-cannula-type RF ablation probe(one example of which is ablation probe 150 of FIG. 1A) with aguideblock has the advantage of reducing obstruction and encumbrancefrom electrode cables and tubes during probe placement, because theelectrodes are not introduced until the cannula are positioned in thepatient body and manipulation of the guideblock and other surgicalguidance tools is complete; this is especially an advantage when it isdesired to use a guideblock with cooled RF ablation probes requiringcoolant tubing, and/or when a stackable guideblock having multiple partsis used. This is a special advantage for ultrasound-guidance andcombined generator-ultrasound imaging systems having multiple ablationprobes (many examples of which are presented in the present invention),because reduction of obstruction to the ultrasound transducer isimportant for proper and smooth ultrasound-guidance. The guideblocks2700, 2760 can also be used with other types of HF ablation probes,including integral RF electrodes and MW antennae. In some embodiments,guideblock 2700 and 2760 can be non-identical, for example havingdifferent but complementary interlock and release features. In someembodiments, each of the guideblocks 2605, 2610, 2615, 2620 of FIG. 26can be adapted to be stackable, for example, by reducing the blockthickness, by include an interlock feature, and/or by including ainterlock release feature. In some embodiments, more than twointerlocking guideblocks can be used to guide probes into the body. Insome embodiments, the guideholes of block 2700 can take the form of aslot.

In accordance with several aspects of the present invention, theguideblocks 2700 and 2760 are one example of a pair of guideblocks thatcan be used in a method for alignment of ablation probes in a body(hereinafter “Method A”) comprising: inserting a first ablation probethrough a first guidehole in a first guideblock, through a secondguidehole in a second guideblock, and into bodily tissue; separating thefirst guideblock and the second guideblock along the shaft of the firstablation probe; inserting a second ablation probe through a thirdguidehole in the first guideblock, through a fourth guidehole in thesecond guideblock, and into the bodily tissue. Method A and furthercomprising: sliding the first guideblock and the second guideblocktoward each other to make room for an ultrasound transducer at thesurface of the bodily tissue. Method A and further comprising: insertinga third ablation probe through a fifth guidehole in the firstguideblock, through a sixth guidehole in the second guideblock, and intothe bodily tissue.

Referring now to FIG. 28, one embodiment of a guideblock 2800 foralignment of two or more ablation probes within a body is presented as aschematic diagram showing three perpendicular external views of theguideblock, in accordance with several aspects of the present invention.The guideblock 2800 is shown in a bottom view labeled “Bottom View”, afirst side view labeled “Side View 1”, and a second view “Side View 2”.The block 2800 includes nine guide-slots through the top-to-bottomthickness T3 of the block 2800. For example slots 2801, 2802, and 2803are shown in the Bottom View. Slot 2801 is visible in Side View 1. Slot2802 is visible in Side View 2. The guideblock 2800 include a centralthrough hole 2804. Each guide-slot (eg 2801, 2802, 2803) cuts throughthe top-to-bottom thickness T3 of the block 2800, is open at one side ofthe block, and has a semi-cylindrical reference surface (eg 2801S,2802S, 2803S, respectively) that is parallel to the othersemi-cylindrical slot reference surfaces and against which an ablationprobe can be guided into bodily tissue in parallel with other ablationprobes that are guided into the bodily tissue against the referencesurfaces of other slots. For example, three ablation proves can beinserted into bodily tissue in a parallel-shaft, equilateral triangleconfiguration by aligning each of the probe against one of the referencesurfaces 2801S, 2802S, and 2803S. Each slot further has a constant widthand follows a path that is equidistant from the center of the guideblock(which is intersects with the central axis of the hole 2804) and that isparallel to the bottom surface of the guideblock 2800. The thickness T3of the block 2800 is less than the minimum distance between thesemi-cylindrical reference surfaces of the guide-slots. As such, afterablation probes, each having a large hub at its proximal end, have beeninserted into bodily tissue through the guideblock 2800, wherein eachprobe is aligned against the reference surface of a slot, the block 2800can be rotated around the axis of the central hole 2804 (for example by30 degrees) such that the probes slide through the slots are exit theside of the block 2800, and the block 2800 can be rotated off thesurface of the bodily tissue onto one of its ends and passed between theablation probes, still inserted in the bodily tissue, providing there issufficient clearance between the block 2800 and the hubs of the probes.One advantage of the block 2800 is that it can be removed after initialalignment of ablation probes in bodily tissue, thereby allowing theprobes to be further advanced into the tissue. In some embodiments, twocopies of block 2800 can be stacked one atop the other, with one blockflipped 180 degrees top over bottom, and thereby produce a combinedguideblock that has cylindrical through holes and that can be removedfrom ablation probes inserted through it into bodily tissue. In someembodiments, said two copies can be adapted to interlock, for example,by the methods and apparatuses shown in relation to blocks 2700 and 2760in FIG. 27. In some embodiments that reference surfaces (eg 2801S,2802S, 2803S) can be a different shape than cylindrical, for exampleflat or a surface having a curvature greater than the width of the slots(eg 2801, 2802, 2803, respectively). In some embodiments, the centralhole 2804 can be omitted.

Paragraph 1: A system for tissue ablation including: a generator ofhigh-frequency signal output; an electrode including an shaft portionadapted to be inserted into the body and adapted to be connected to thegenerator, the shaft portion having a tip portion so adapted such thatwhen said shaft portion is inserted into the body, the signal output isdelivered through the tip portion to the bodily tissue to be ablated,said shaft portion having an inner space that can accept circulation ofcoolant to cool said tip portion; a coolant system adapted to connect tosaid electrode and supply circulation of coolant to the electrode innerspace to cool the electrode tip portion; a measuring system adapted tomeasure in real time at least one signal output parameter from the listof impedance, current, voltage, and power; a control system including anautomatic controller adapted to control the at least one measured signaloutput parameter, including modulating the signal output to maintain theat least one measured signal output parameter at a desired level; acomputer graphic display adapted to plot in real time at least onemeasured signal output parameter as a function of a time scale axis.

Paragraph 2: The system of Paragraph 1 wherein the measuring systemmeasures in real time at least two signal output parameters from thelist of impedance, current, voltage, and power; and wherein the computergraphic display plots in real time at least two measured signal outputparameters on the same time scale, either next to each other on separatetime scale axes, or overlapping each other on the same time scale axis,to provide a dynamic visual relationship of the variation of thesesignal output parameters.

Paragraph 3: The system of Paragraph 1 wherein the control systemswitches the level of the signal output between an ablation rangeconfigured to heat tissue substantially, and a cooling range configuredto allow for cooling of the heated tissue, wherein the control systemperforms the switching in response to at least one of the measuredsignal output parameter in accordance with the automatic controller.

Paragraph 4: The system of Paragraph 1 wherein the control systemalternately switches the level of the signal output between an ablationrange configured to provide for substantial tissue heating, and acooling range configured to provide for tissue, and thereby produces asequence of signal output levels configured to maintain at least one ofthe measured signal output parameters in a desired range, in accordancewith the automatic controller.

Paragraph 5: The system of Paragraph 1 wherein the control systemproduces a sequence of up times and down times; wherein during each uptime, the signal output level is set to a high level configured to raisetissue temperatures substantially; wherein during each down time, thesignal output level is set to a low level configured to allow forcooling of tissue cool that was heated into the boiling range; andwherein the control system, according to the automatic controller,stabilizes the duration of the up times, the duration of down times, andthe signal output level during the up times to achieve a desiredablation size for a prescribed total duration of the ablation process.

Paragraph 6: The system of Paragraph 5 wherein the durations of the uptimes and the durations of the down times are each stabilized to a valuein the range 5 to 40 seconds.

Paragraph 7: The system of Paragraph 1 wherein the control system, bymeans of the automatic controller, begins the process of abating tissueby means of the electrode by automatically ramping up the signal outputlevel until the at least one signal output parameter reaches aprescribed level, and then the control system continues the process ofablating tissue by automatically modulating the signal output levelaccording to the automatic controller to maintain at least one measuredsignal output parameter at desired levels to optimize ablation size.

Paragraph 8: The system of Paragraph 1 wherein the tip portion containsa temperature sensor; wherein the measuring system includes atemperature measuring system adapted to connect to the temperaturesensor and to produce a temperature signal indicative of the temperaturein the tip portion; wherein the computer graphic display is adapted toplot the temperature signal in real time on the same time scale as thetime scale of a plotted signal output parameter.

Paragraph 9: The system of Paragraph 1 wherein the computer graphicdisplay plots in real time either power, or current, or both, and atleast one additional parameter selected from the list voltage,impedance, and temperature, as a function of the same time scale axis.

Paragraph 10: The system of Paragraph 9 wherein the graphic displayparameters is color-coded so the parameters can be easily visuallydifferentiated from each other.

Paragraph 11: The system of Paragraph 1 wherein the range of the timescale axis is at least 720 seconds.

Paragraph 12: The system of Paragraph 1 wherein if one of the displayedsignal output parameters is impedance, then the range of the impedancemeasurement includes at least the range 40 to 120 ohms.

Paragraph 13: The system of Paragraph 1 wherein if one of the displayedsignal output parameters is current, then the range of said currentoutput measurement includes at least the range 0 to 2000 mA.

Paragraph 14: The system of Paragraph 1 wherein the generator canproduce more than 50 Watts of high-frequency signal output.

Paragraph 15: The system of Paragraph 1 wherein the generator canproduce at least 200 Watts of high-frequency signal output.

Paragraph 16: The system of Paragraph 1 wherein the generator canproduce at least 400 Watts of high-frequency signal output.

Paragraph 17: The system of Paragraph 1 wherein the generator isconfigured for tumor ablation.

Paragraph 18: The system of Paragraph 5 wherein during each up time, thesignal output is on; and wherein during each down time, the signaloutput is off.

Paragraph 19: A system for ablation of tissue in the body including agenerator of radiofrequency or microwave signal output; an electrodeincluding a shaft portion adapted to be inserted into tissue of a bodyand adapted to be connected to the generator, the shaft portion having atip portion so adapted that when the shaft portion is inserted into thebody, the signal output is delivered through the tip portion to thetissue to be ablated, said shaft portion having an inner space that canaccept circulation of coolant to cool said tip portion; a coolant systemadapted to connect to said electrode and supply circulation of coolantto the inner space to cool said tip portion; a measuring system adaptedto measure in real time the impedance of the signal output and at leastone signal output level parameter in the list of power, voltage, andcurrent; a control system including an automatic controller adapted tocontrol the impedance, wherein the automatic controller modulates atleast one of the signal output level parameters in the list of power,voltage, and current, wherein the modulation is configured to maintainthe impedance at desired levels; a computer graphic display adapted toplot in real time the impedance on a first time axis, and the at leastone measured signal output level parameter on a second time axis,wherein the time axes are registered to the same time scale to provide adynamic visual relationship of the variation of the impedance and the atleast one measured signal output level parameter.

Paragraph 20: The system of Paragraph 19 wherein the time axis of theimpedance and the time axis of the at least one measured signal outputlevel parameter are positioned next to each other.

Paragraph 21: The system of Paragraph 19 wherein the time axis of theimpedance and the time axis of the at least one measured signal outputlevel parameter are the same time axis.

Paragraph 22: The system of Paragraph 19 wherein the control systemswitches the level of the signal output between an ablation rangeconfigured to heat tissue substantially, and a cooling range configuredto allow for cooling of the heated tissue, wherein the control systemperforms the switching in response to the impedance, in accordance withthe automatic controller.

Paragraph 23: The system of Paragraph 19 wherein the modulation ofsignal output level by the automatic controller includes repeatedalternations of up times wherein the signal output is higher, and downtimes wherein the signal output is lower, to achieve a stable pattern ofimpedance, output level modulations, up-time durations, and down-timedurations, until an overall duration of signal output has been deliveredto produce a desired ablation size; wherein during each up time, bymeans of the automatic controller, the control system maintains orincreases the output level until the impedance rises above a thresholdvalue; wherein during each down time, by means of the automaticcontroller, the control system produces a low output level for aduration configured to reduce the impedance to a baseline value.

Paragraph 24: The system of Paragraph 23 wherein the output signal isshut off during each down time; and wherein the output signal is turnedon during each up time.

Paragraph 25: The system of Paragraph 19 wherein the tip portioncontains a temperature sensor; wherein the measuring system includes atemperature measuring system adapted to connect to the temperaturesensor and to produce a temperature signal indicative of the temperaturein the tip portion; wherein the computer graphic display is adapted toplot the temperature signal in real time on the same time scale as thetime scale of the impedance and the at least one measured signal outputlevel parameter.

Paragraph 26: The system of Paragraph 25 wherein the measuring system isadapted to measure the parameters impedance, current, voltage, power,and temperature, and the computer graphic display is adapted to plot allof these parameters in real time, and on the same time scale axis.

Paragraph 27: The system of Paragraph 25 wherein the plots of themeasured parameters are color coded so they can be easily visuallydifferentiated.

Paragraph 28: The system of Paragraph 23 wherein after repeatedalternations of up time and down time, the duration of the up times andthe duration of the down times both stabilize to values in the range 5to 40 seconds.

Paragraph 29: The system of Paragraph 19 wherein each time axis has arange of at least 720 seconds.

Paragraph 30: The system of Paragraph 19 wherein the range of impedancemeasurement includes at least the range 40 to 120 ohms.

Paragraph 31: The system of Paragraph 19 wherein if current is one ofthe measured signal output level, then current-measurement rangeincludes at least the range 0 to 2000 mA.

Paragraph 32: The system of Paragraph 19 wherein the electrode shaftportion includes a metal tube that is insulated over its surface exceptfor the tip portion which is uninsulated so that when said shaft portionis inserted into the tissue of the body, and said generator is connectedelectrically to the metal tube of the shaft portion, then the signaloutput current flows into the tissue only from of the tip portion toproduce heating of the tissue.

Paragraph 33: The system of Paragraph 19 wherein a surface portion ofthe electrode tip portion is made echogenic by a surface treatment thatreflects ultrasound signals preferentially so that when an ultrasoundimaging machine is used to image bodily tissue in which the electrodetip portion is inserted, the echogenic surface portion is prominentlyvisible to indicate the position of the tip portion in the tissue.

Paragraph 34: The system of Paragraph 33 wherein the echogenic surfaceportion includes a multiplicity of surface indentations in the surfaceof the tip portion.

Paragraph 35: A system for tissue ablation that includes aradiofrequency generator and a graphic display, wherein theradiofrequency generator is configured to apply a radiofrequency signalto an ablation electrode that is in contact with bodily tissue; whereinthe graphic display is configured plot in real time and on one timeaxis, two or more parameters of the signal delivered to the ablationelectrode; wherein each parameter is selected from the list: impedance;voltage; current; power; a measurement of the signal; mathematicalfunctions taking one or more of the arguments impedance, voltage,current, power, and a measurement of the signal.

Paragraph 36: The system of Paragraph 35 and further including acontroller configured to automatically alternate the signal levelbetween a first range configured to heat tissue, and a second rangeconfigured to allow for cooling of heated tissue.

Paragraph 37: The system of Paragraph 36 wherein the controller switchesthe signal level from the first range to the second range based in wholeor in part on an indication of boiling or impending boiling in tissueheated by the ablation electrode, and wherein the controller switchesthe signal level from the second range to the first range after aduration configured to allow for dissipation of gas bubbles formed inthe tissue due to boiling.

Paragraph 38: The system of Paragraph 36 wherein the controller changesthe signal level from the first range to the second range based in wholeor in part on an increase in a measured impedance.

Paragraph 39: The system of Paragraph 38 wherein one of the plottedparameters is impedance, one of the plotted parameters is current, andthe first range is a range of radiofrequency current levels.

Paragraph 40: The system of Paragraph 36 wherein the controller changesthe signal level from the first range to the second range based in wholeor in part on a change in one or more measured parameters in the listvoltage, current, power.

Paragraph 41: The system of Paragraph 36 wherein the controller changesthe signal level from the second range to the first range based on inwhole or in part a measured impedance.

Paragraph 42: The system of Paragraph 36 wherein the ablation electrodeis internally-cooled and the controller is configured to optimize aparameter of tissue heating by the ablation electrode.

Paragraph 43: The system of Paragraph 36 wherein the ablation electrodeis internally-cooled and the controller is configured to maximize thevolume of tissue heated by the internally-cooled ablation electrode.

Paragraph 44: The system of Paragraph 36 wherein the first range is arange of signal levels of one type, wherein the type is selected fromthe list current, power, voltage.

Paragraph 45: The system of Paragraph 36 wherein the first range is arange radiofrequency current values.

Paragraph 46: The system of Paragraph 35 wherein the ablation electrodeis internally-cooled.

Paragraph 47: The system of Paragraph 35 wherein the ablation electrodeis not internally-cooled.

Paragraph 48: The system of Paragraph 35 wherein the ablation electrodeincludes a temperature sensor.

Paragraph 49: The system of Paragraph 35 wherein the ablation electrodedoes not include a temperature sensor.

Paragraph 50: The system of Paragraph 35 wherein one of the plottedparameters is impedance.

Paragraph 51: The system of Paragraph 35 wherein one of the plottedparameters is current.

Paragraph 52: The system of Paragraph 35 wherein one of the plottedparameters is impedance, and one of the plotted parameters is current.

Paragraph 53: The system of Paragraph 35 wherein the graphic display isfurther configured to plot a temperature of the ablation electrode inreal time on the time axis.

Paragraph 54: The system of Paragraph 35 wherein one of the plottedparameters is impedance, one of the plotted parameters is current, andthe graphic display is further configured to plot a temperature of theablation electrode in real time on the time axis.

Paragraph 55: The system of Paragraph 35 wherein the graphic display isfurther configured to plot a temperature measured at a distance from theablation electrode.

Paragraph 56: The system of Paragraph 35 and further including acontroller that can automatically regulate the signal level delivered tothe ablation electrode, wherein the signal level is a parameter of thesignal selected from the list: impedance; voltage; current; power, ameasurement of the signal; a mathematical function taking one or more ofthe arguments impedance, voltage, current, power, and a measurement ofthe signal.

Paragraph 57: The system of Paragraph 35 wherein the radiofrequencygenerator delivers one or more radiofrequency signals to one or moreablation electrodes, and for each ablation electrode, the graphicdisplay plots in real time and on a time axis, two or more parameters ofthe signal delivered to the ablation electrode; wherein each parameteris selected from the list: impedance; voltage; current; power; ameasurement of the signal delivered to the ablation electrode;mathematical functions taking one or more of the arguments impedance,voltage, current, power, and a measurement of the signal delivered tothe ablation electrode.

Paragraph 58: The system of Paragraph 57 wherein the graphic displaypositions all the plots of more than one electrode on the same timeaxis.

Paragraph 59: The system of Paragraph 57 wherein the graphic displayincludes a different time axis for the plots of each of the one or moreablation electrodes.

Paragraph 60: A system for tissue ablation that includes aradiofrequency generator, a controller, and a graphic display, whereinthe radiofrequency generator delivers a radiofrequency signal output toan electrode inserted into bodily tissue; wherein the controllerautomatically alternates between a first state and a second state;wherein in the first state, the controller maintains the signal outputat a higher level configured to raise the temperature of a substantialportion of the bodily tissue to a destructive temperature; wherein inthe second state, the controller maintains the signal output at a lowerlevel configured to allow the temperature of heated bodily tissue tocool substantially; wherein the graphic display plots one or moreparameters of the signal output as a function of time; wherein eachparameter can be selected from the list: impedance, current, power,voltage, duty cycle, temperature, time, a signal output level, ameasurement of the signal output, a parameter of the signal output, atime average of a parameter of the signal output, the RMS value of aparameter of the signal output over a time window, a mathematicalfunction of one or more parameters of the signal output.

Paragraph 61: The system of Paragraph 60 and further including a coolantsupply, wherein the electrode is cooled by the coolant supply.

Paragraph 62: The system of Paragraph 60 or Paragraph 61 wherein thecontroller switches from the first state to the second state when ameasurement indicates the presence of high-temperature vapor in tissuenear the electrode.

Paragraph 63: The system of Paragraph 60 or Paragraph 61 wherein thecontroller switches from the first state to the second state in responseto a change in a measured impedance.

Paragraph 64: The system of Paragraph 60 or Paragraph 61 wherein theduration for which the controller remains in the second state beforeswitching to the first state is configured to provide for dissipation ofhigh-temperature vapor in tissue near the electrode active tip.

Paragraph 65: The system of Paragraph 60 or Paragraph 61 wherein thecontroller prevents switching from the second state to the first stateunless an elevated impedance decreases to a lower value.

Paragraph 66: The system of Paragraph 60 or Paragraph 61 wherein thehigher level is an RF current level or a range of RF current levels.

Paragraph 67: The system of Paragraph 60 or Paragraph 61 wherein thehigher level is an RF power level or a range of RF power levels.

Paragraph 68: The system of Paragraph 60 or Paragraph 61 wherein thehigher level is an RF voltage level or a range of RF voltage levels.

Paragraph 69: The system of Paragraph 60 or Paragraph 61 wherein theduration of an instance of the first state or of an instance of thesecond state is greater than 5 seconds.

Paragraph 70: A system for tissue ablation that includes aradiofrequency generator and a controller, wherein the radiofrequencygenerator is configured to deliver a radiofrequency signal to bodilytissue via a radiofrequency electrode; wherein the controllerautomatically produces a sequence of on periods and off periods; whereinduring each on period, the controller configures the signal level toheat tissue in order to increase the volume ablated tissue; whereinduring each off period, the controller configures the signal level toallow for cooling of heated tissue; wherein after the signal is firstconfigured to heat tissue in order to increase the volume ablatedtissue, the controller both increases and decreases the signal leveldelivered during on periods.

Paragraph 71: The system of Paragraph 70 wherein the radiofrequencyelectrode is internally-cooled.

Paragraph 72: The system of Paragraph 70 wherein the duration of atleast one on period or off period is 5 seconds or longer.

Paragraph 73: The system of Paragraph 70 wherein the controller switchesfrom an on period to an off period is based in whole or in part on anindication of tissue boiling.

Paragraph 74: The system of Paragraph 70 wherein the controller switchesfrom an on period to an off period is based in whole or in part on animpedance.

Paragraph 75: The system of Paragraph 70 wherein the controllerconfigures the duration of an off period to provide for dissipation ofgaseous vapor formed by boiling within the tissue.

Paragraph 76: The system of Paragraph 70 wherein the controllerregulates a parameter of the signal level during each on period, whereinthe parameter is selected from the list current, voltage, power.

Paragraph 77: The system of Paragraph 70 wherein the controllerautomatically regulates a parameter of the signal level during each offperiod, wherein the parameter is selected from the list current,voltage, power.

Paragraph 78: The system of Paragraph 70 wherein the controllerincreases the signal level during an on period.

Paragraph 79: The system of Paragraph 78 wherein the controllerincreases the signal level in steps over time.

Paragraph 80: The system of Paragraph 79 wherein the controller sets theinitial signal level of an on period to be less than the final signallevel of the latest preceding on period by an amount that is influencedby the duration of the final step in the signal level during the latestpreceding on period.

Paragraph 81: The system of Paragraph 79 wherein a step increase in thesignal level during a first on period is reversed by the controller toset the initial signal level for the next on period, if the duration ofthe step increase is less than a threshold value.

Paragraph 82: The system of Paragraph 78 wherein the controllerincreases the signal level as a smooth function of time after a delay ofat least zero seconds.

Paragraph 83: The system of Paragraph 78 wherein the controller sets theinitial signal level of a first on period to be less than the finalsignal level of the last preceding on period, wherein the differencebetween the final signal level of the last preceding on period and theinitial signal level of the first on period is influenced by theduration and degree of signal level increase during the last precedingon period.

Paragraph 84: The system of Paragraph 70 wherein the signal level duringa first on period is less than the signal level during a second onperiod, wherein the first on period comes before the second on period.

Paragraph 85: The system of Paragraph 84 wherein the increase in signallevel from the first on period to the second on period is influenced bythe duration of the first on period.

Paragraph 86: The system of Paragraph 70 wherein the controller sets theinitial signal level of an on period to a value that is less than thefinal signal level of the latest preceding on period, wherein the valueis influenced a parameter of the latest preceding on period.

Paragraph 87: The system of Paragraph 70 wherein the controller sets theinitial signal level of an on period to a value that is less than thefinal signal level of the latest preceding on period if the duration ofthe latest preceding on period is less than a threshold value.

Paragraph 88: The system of Paragraph 70 wherein the increases anddecreases in the signal level delivered during on periods are configuredto maximize the volume ablated tissue.

Paragraph 89: The system of Paragraph 70 wherein the increases anddecreases in the signal level delivered during on periods are configuredto optimize a feature of the ablation process.

Paragraph 90: The system of Paragraph 70 further including a first usersetting that sets the initial signal level of the initial on period inthe sequence, and a second user setting that sets the maximum signallevel of all on periods in the sequence.

Paragraph 91: A system for tissue ablation that includes aradiofrequency generator and a controller; wherein the radiofrequencygenerator is configured to deliver a radiofrequency signal to bodilytissue via a radiofrequency electrode; wherein the controllerautomatically produces a sequence of on periods and off periods; whereinduring each on period, the controller configures the signal level toheat tissue in order to increase the volume ablated tissue; whereinduring each off period, the controller configures the signal level toallow for cooling of heated tissue; wherein the duration of a first offperiod is different from the duration of a second off period.

Paragraph 92: The system of Paragraph 91 wherein the controller switchesfrom an on period to an off period when continued application of thesignal level of the on period no longer increases volume of ablatedtissue; wherein the controller increases the duration of an off periodrelative to the duration of a preceding off period if the duration of apreceding on period is less than a threshold value.

Paragraph 93: The system of Paragraph 91 wherein the controllerincreases the duration of the off periods monotonically as a function ofthe elapsed time of the sequence.

Paragraph 94: The system of Paragraph 91 wherein the controller sets theduration of an off period as a function of a measurement of tissuetemperature at a distance from the electrode active tip.

Paragraph 95: The system of Paragraph 91 wherein the controller sets theduration of an off period as a function of an impedance measurement.

Paragraph 96: The system of Paragraph 91 wherein the controller sets theduration of the off period as a function of the duration over which animpedance decreases from an elevated level induced by tissue heatingduring the previous on period.

Paragraph 97: A system for tissue ablation that includes aradiofrequency generator and a controller; wherein the radiofrequencygenerator is configured to deliver a radiofrequency signal to bodilytissue via a radiofrequency electrode; wherein the controllerautomatically produces a sequence of on periods and off periods; whereinduring each on period, the controller configures the signal level toheat tissue in order to increase the volume ablated tissue; whereinduring each off period, the controller configures the signal level toallow for cooling of heated tissue; wherein after the signal is firstconfigured to heat tissue, the controller both increases and decreasesthe signal level delivered during on periods; and wherein the durationof a first off period is different from the duration of a second offperiod.

Paragraph 98: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse when there is an indication of tissueboiling; after the beginning of the initial pulse of the sequence,increasing the radiofrequency signal amplitude delivered during a pulserelative to an earlier radiofrequency signal amplitude delivered duringa pulse; and decreasing the radiofrequency signal amplitude deliveredduring a pulse relative to an earlier radiofrequency signal amplitudedelivered during a pulse.

Paragraph 99: The method of Paragraph 98 wherein the indication oftissue boiling includes the impedance encountered by the pulse currentrising above an impedance threshold.

Paragraph 100: The method of Paragraph 98 performed in whole or in partby an automated controller.

Paragraph 101: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse based in whole or in part on an indicationof tissue boiling; generating a pulse that includes a higherradiofrequency signal amplitude than does a preceding pulse.

Paragraph 102: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse when tissue boiling is detected; setting theduration an inter-pulse period to be different from the duration of anearlier inter-pulse period.

Paragraph 103: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse based in whole or in part on an indicationof tissue boiling; after the beginning of the initial pulse of thesequence, increasing the radiofrequency signal amplitude deliveredduring a pulse relative to an earlier radiofrequency signal amplitudedelivered during a pulse; decreasing the radiofrequency signal amplitudedelivered during a pulse relative to an earlier radiofrequency signalamplitude delivered during a pulse; and setting the duration aninter-pulse period to be different from the duration of an earlierinter-pulse period.

Paragraph 104: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse based in whole or in part on an indicationof tissue boiling; and stopping the sequence when the number ofradiofrequency pulses exceeds a count threshold.

Paragraph 105: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse when tissue boiling is detected; andstopping the sequence when the sum of the durations of generated pulsesexceeds a time threshold.

Paragraph 106: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse when there is an indication of tissueboiling; and stopping the sequence if the time-integrated mean-squaredradiofrequency current delivered during the sequence exceeds a currentthreshold.

Paragraph 107: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse when a measurement indicated tissue boiling;and stopping the sequence if the time-integrated radiofrequency powerdelivered during the sequence exceeds a power threshold.

Paragraph 108: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse when there is an indication of tissueboiling; and stopping the sequence if the total energy delivered duringthe sequence exceeds an energy threshold.

Paragraph 109: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse based in whole or in part on a measurementindicative of tissue boiling; reducing the amplitude of a pulse if theduration of a preceding pulse is less than a time threshold; andstopping the sequence if the amplitude of a pulse falls below anamplitude threshold.

Paragraph 110: The method of Paragraph 109 further comprising: adjustingthe value of the amplitude threshold based in whole or in part on theamplitude of a preceding pulse.

Paragraph 111: The method of Paragraph 109 further comprising: settingthe value of the amplitude threshold relative to the maximum pulseamplitude of the sequence.

Paragraph 112: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse based in whole or in part on an indicator oftissue boiling; reducing the amplitude of a pulse or increasing theduration of an inter-pulse period if the duration of a preceding pulseis less than a duration threshold; stopping the sequence if the averageradiofrequency signal amplitude over at least one consecutive pulse andinter-pulse period is less than an amplitude threshold, wherein theamplitude threshold is a function of a parameter selected from the listcurrent, power, voltage.

Paragraph 113: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse is conditioned on an indicator of tissueboiling; increasing the duration of an inter-pulse period if theduration of a preceding pulse is less than a time threshold; andstopping the sequence if the duty cycle over at least one consecutivepulse and inter-pulse period is less than a duty-cycle threshold.

Paragraph 114: A method of pulsed-radiofrequency, cooled-radiofrequencytissue ablation comprising: generating a sequence of radiofrequencypulses; terminating a pulse based in whole or in part on an indicationof tissue boiling; increasing the duration of an inter-pulse period ifthe duration of a preceding pulse is below a first time threshold; andstopping the sequence if the duration of an inter-pulse period isgreater than an second time threshold.

Paragraph 115: A system for tissue ablation including a radiofrequencysignal generator, an ablation electrode, at least two ground pads, andcurrent-measurement circuit for each ground pad; wherein current fromthe radiofrequency signal generator flows between the electrode and eachground pad through a living body at the same time; wherein the systemmeasures the current flowing through each ground pad.

Paragraph 116: A system for tissue ablation that includes aradiofrequency signal generator, a user interface, an ablationelectrode, at least two ground pads, and a current-measurement system;wherein current from the radiofrequency signal generator flows betweenthe electrode and each ground pad through a living body; wherein thecurrent-measurement system measures the current flowing through eachground pad; and wherein the user interface includes a display for aground pad.

Paragraph 117: The system of Paragraph 116 wherein the display for aground pad includes a display of the current flowing through the groundpad.

Paragraph 118: The system of Paragraph 116 wherein the display for aground pad includes a display of the RMS value of the radiofrequencycurrent flowing through the ground pad.

Paragraph 119: The system of Paragraph 116 wherein the display for aground pad includes a display of the impedance between the ablationelectrode and the ground pad.

Paragraph 120: The system of Paragraph 116 wherein the display for aground pad includes a display of the temperature of the ground pad.

Paragraph 121: The system of Paragraph 116 wherein the display for aground pad includes a display of the portion of the total currentflowing through all ground pads, that is flowing to the ground pad.

Paragraph 122: The system of Paragraph 121 wherein the portion isdisplayed as a fraction, a percentage, a fraction relative to a desiredfraction, a fraction minus the quotient of one (I) divided by the totalnumber of ground pads, a percentage relative to a desired percentage, ora percentage minus the quotient of one hundred (100) dividend by thetotal number of ground pads.

Paragraph 123: The system of Paragraph 116 wherein the display for aground pad includes a display of a quotient wherein the dividend is thecurrent flowing through the ground pad and the devisor is the totalcurrent flowing through all ground pads.

Paragraph 124: The system of Paragraph 116 wherein the display for aground pad includes a display of a measurement of the portion of thetotal radiofrequency current flowing to all ground pads, that is flowingto the ground pad.

Paragraph 125: The system of Paragraph 116 wherein the display for aground pad includes a display of a mathematical function of the currentflowing through the ground pad and the current flowing through anotherground pad.

Paragraph 126: The system of Paragraph 116 wherein the display for aground pad includes a display of an average of the current flowingthrough the ground pad over a time window.

Paragraph 127: The system of Paragraph 116 wherein the display for aground pad includes a display of the root-mean-square average of thecurrent flowing through the ground pad over a time window.

Paragraph 128: The system of Paragraph 116 wherein the display for aground pad includes a numerical display.

Paragraph 129: The system of Paragraph 116 wherein the display for aground pad includes a digital display.

Paragraph 130: The system of Paragraph 116 wherein the display for aground pad includes a graphical display.

Paragraph 131: The system of Paragraph 116 wherein the display for aground pad includes a bar graph.

Paragraph 132: The system of Paragraph 116 wherein the display for aground pad includes a plot of a measured parameter of the ground pad asfunction of a time axis.

Paragraph 133: The system of Paragraph 116 wherein the user interfaceincludes a display for each ground pad.

Paragraph 134: The system of Paragraph 116 and further including aswitch for each ground pad wherein opening a switch disconnects a groundpad from the radiofrequency signal generator and substantially stops theflow of current from the radiofrequency signal generator through theground pad, and wherein closing a switch connects a ground pad to theradiofrequency signal generator and allows the flow of current from theradiofrequency signal generator through the ground pad; and furtherincluding a controller that automatically opens and closes the switch ofa ground pad to regulate the displayed parameter for the ground pad.

Paragraph 135: The system of Paragraph 134 wherein the display for aground pad includes a display of a moving average of the current flowingthrough the ground pad over at least one time period during which atleast one ground-pad switch either opens or closes.

Paragraph 136: The system of Paragraph 134 wherein the display for aground pad includes a display of a root-mean-square moving average ofthe current flowing through the ground pad over at least one time windowduring which at least one ground-pad switch either opens or closes.

Paragraph 137: The system of Paragraph 116 and further including morethan one ablation electrode wherein current from the radiofrequencysignal generator flows between each electrode and each ground padthrough the living body.

Paragraph 138: The system of Paragraph 116 and further including anerve-stimulation signal generator wherein current from thenerve-stimulation signal generator flows between the electrode and atleast one of the ground pads through the living body.

Paragraph 139: A method for distributing radiofrequency current from anablation electrode, through a living body, between at least two groundpads comprising: measuring the current flowing through a ground pad, anddisplaying the measured current in real-time.

Paragraph 140: The method of Paragraph 139 wherein the measured currentis displayed numerically, digitally, by an analog indicator,graphically, as a bar graph, as a line graph, or as a function of a timeaxis.

Paragraph 141: The method of Paragraph 139 wherein the measured currentis displayed as a value of the measured current at an instant in time,an average value of the measured current over a time period, a movingaverage of the measured current, the root-mean-squared average of themeasured current over a time period, the root-mean-square average of themeasured current over a moving time window, a fraction, a percentage, afraction relative to a desired fraction, a percentage relative to adesired percentage, the portion of the current flowing through theablation electrode that is flowing through the ground pad, a quotientwherein the dividend is the current flowing through the ground pad andthe devisor is the total current flowing through all ground pads, or amathematical function of the current flowing through the ground pad andthe current flowing through at least one other ground pad.

Paragraph 142: A system for tissue ablation including a radiofrequencysignal generator, a nerve-stimulation signal generator, at least oneablation electrode connected to a first pole of the radiofrequencysignal generator, at least two ground pads connected to a second pole ofthe radiofrequency signal generator, and a circuit that measures thecurrent of each ground pad; wherein, in a first operating mode, currentfrom the radiofrequency signal generator flows between at least oneablation electrode and each ground pad through a living body; wherein,in a second operating mode, current from the nerve-stimulation signalgenerator flows between at least one ablation electrode and at least oneof the ground pads through the living body.

Paragraph 143: The system of Paragraph 142 wherein the first operatingmode and the second operating mode are active at the same time.

Paragraph 144: The system of Paragraph 142 wherein the first operatingmode and the second operating mode are not active at the same time.

Paragraph 145: The system of Paragraph 142 and further including a userinterface that includes a display of the current flowing through aground pad.

Paragraph 146: The system of Paragraph 142 wherein the radiofrequencysignal generator can produce more than 50 Watts of power.

Paragraph 147: The system of Paragraph 142 wherein the number ofablation electrodes is greater than four.

Paragraph 148: The system of Paragraph 142 and further including acontroller and a switch; wherein a ground pad is connected to theradiofrequency signal generator through the switch; wherein thecontroller alternately connects and disconnects the ground pad from theradiofrequency signal generator by means of the switch.

Paragraph 149: The system of Paragraph 148 wherein the controlleralternately connects and disconnects the ground pad from theradiofrequency signal generator to regulate the current flowing throughthe ground pad.

Paragraph 150: The system of Paragraph 148 wherein the controlleralternately connects and disconnects the ground pad from theradiofrequency signal generator to regulate the temperature of tissue incontact with the ground pad.

Paragraph 151: The system of Paragraph 148 wherein the controllerdisables the radiofrequency signal generator while the switch is in theprocess of connecting or disconnecting the ground pad from theradiofrequency signal generator.

Paragraph 152: The system of Paragraph 142 and further including acontroller and a switch; wherein a ground pad is connected to thenerve-stimulation signal generator through the switch; wherein thecontroller alternately connects and disconnects the ground pad from thenerve-stimulation signal generator by means of the switch.

Paragraph 153: The system of Paragraph 152 wherein the controllerdisables the nerve-stimulation signal generator while the switch is inthe process of connecting or disconnecting the ground pad from thenerve-stimulation signal generator.

Paragraph 154: The system of Paragraph 142 and further including acontroller and a switch; wherein an ablation electrode is connected tothe radiofrequency signal generator through the switch; wherein thecontroller alternately connects and disconnects the ablation electrodefrom the radiofrequency signal generator by means of the switch.

Paragraph 155: The system of Paragraph 154 wherein the controllerdisables the radiofrequency signal generator while the switch is in theprocess of connecting or disconnecting the ablation electrode from theradiofrequency signal generator.

Paragraph 156: The system of Paragraph 142 and further including acontroller and a switch; wherein an ablation electrode is connected tothe nerve-stimulation signal generator through the switch; wherein thecontroller alternately connects and disconnects the ablation electrodefrom the nerve-stimulation signal generator by means of the switch.

Paragraph 157: The system of Paragraph 156 wherein the controllerdisables the nerve-stimulation signal generator while the switch is inthe process of connecting or disconnecting the ablation electrode fromthe nerve-stimulation signal generator.

Paragraph 158: A system for tissue ablation that includes aradiofrequency signal generator, a controller, an ablation electrode, atleast two ground pads, and circuit that measures the current of eachground pad; wherein current from the radiofrequency signal generatorflows between the electrode and each ground pad through a living body atthe same time; and wherein the controller automatically produces asequence in which a ground pad is repeatedly connected to anddisconnected from the radiofrequency signal generator by a switch toregulate the current of the ground pad during a tissue ablation process.

Paragraph 159: A system for tissue ablation that includes aradiofrequency signal generator, a controller, an ablation electrode, atleast two ground pads, and an individual current-measurement device foreach ground pad; wherein current from the radiofrequency signalgenerator flows between the electrode and each ground pad through aliving body; and wherein the controller automatically produces asequence in which a ground pad is alternately connected and disconnectedfrom the radiofrequency signal generator during a tissue ablationprocess.

Paragraph 160: A system for tissue ablation that includes aradiofrequency signal generator, a controller, an ablation electrode, atleast two ground pads, and a switch between each ground pad and theradiofrequency signal generator; wherein the controller automaticallygenerates a sequence that includes at least two steps; wherein, in afirst step having a first duration, the switch for a first ground pad isclosed, the switch for a second ground pad is closed, and currentgenerated by the radiofrequency signal generator flows from the ablationelectrode to both a first ground pad and a second ground pad through aliving body; wherein, in a second step having a second duration, theswitch for the first ground pad is open, the switch for the secondground pad is closed, current from the radiofrequency signal generatordoes not flow substantially through the first ground pad, and currentgenerated by the radiofrequency signal generator flows from the ablationelectrode to the second ground pad through the living body; wherein theidentity of the first ground pad is not predetermined.

Paragraph 161: The system of Paragraph 160 wherein the controllermeasures the current flowing through each ground pad during the firststep, and the controller determines the identity of the first ground padas that ground pad which has the higher current measurement.

Paragraph 162: The system of Paragraph 160 wherein the controllermeasures the current flowing through each ground pad before the secondstep, and the controller determines the identity of the first ground padas that ground pad which has the higher current measurement.

Paragraph 163: The system of Paragraph 160 wherein the controllermeasures the temperature of each ground pad, and the controllerdetermines the identity of the first ground pad as that ground pad whichhas the higher temperature measurement.

Paragraph 164: The system of Paragraph 160 wherein the controllerdetermines the identity of the first ground pad, the identity of thesecond ground pad, the duration of the first step, the duration of thesecond step, the number of repetitions of the first step, or the numberof repetitions of the second step in order to regulate a parameterinfluenced by the current flowing through a ground pad.

Paragraph 165: The system of Paragraph 164 wherein the controllerdetermines the identity of the first ground pad or the identity of thesecond ground pad in order to reduce the number of steps in thesequence, to increase of the number of switches closed at the same time,to increase the duration for which more switches are closed at the sametime, to increase the duration for which all switches are closed at thesame time, or to reduce the duration during which only one switch isclosed.

Paragraph 166: The system of Paragraph 160 wherein the first stepprecedes the second step.

Paragraph 167: The system of Paragraph 160 wherein the second stepprecedes the first step.

Paragraph 168: A system for tissue ablation that includes aradiofrequency signal generator, a controller, an ablation electrode,and at least two ground pads; wherein the controller automaticallygenerates a sequence of at least two configurations; wherein, in a firstconfiguration having a first duration, both a first ground pad and asecond ground pad are connected to the radiofrequency signal generator,and current generated by the radiofrequency signal generator flows fromthe ablation electrode to both the first ground pad and the secondground pad through a living body; wherein, in a second configurationhaving a second duration, the first ground pad is disconnected from theradiofrequency signal generator, the second ground pad is connected tothe radiofrequency signal generator, current generated by theradiofrequency signal generator flows from the ablation electrode to thesecond ground pad through the living body, and current from theradiofrequency signal generator does not flow substantially through thefirst ground pad; the identity of the first ground pad is notpredetermined.

Paragraph 169: The system of Paragraph 168 wherein the controllerselects the duration of the first configuration, the duration of thesecond configuration, the identity of the first ground pad, or theidentity of the second ground pad based in whole or in part on ameasured parameter of a ground pad.

Paragraph 170: The system of Paragraph 168 wherein the time schedule ofthe sequence is not predetermined.

Paragraph 171: The system of Paragraph 168 wherein at no time in thesequence does the controller switch an application of voltage firstbetween the ablation electrode and the first ground pad, and secondbetween the ablation electrode and the second ground pad.

Paragraph 172: The system of Paragraph 168 wherein the controllerconfigures the sequence to regulate a parameter of a ground pad.

Paragraph 173: The system of Paragraph 172 wherein the parameter of aground pad is the current carried by the ground pad.

Paragraph 174: The system of Paragraph 172 wherein the parameter of aground pad is the root-mean-squared current carried by the ground pad.

Paragraph 175: The system of Paragraph 172 wherein the parameter of aground pad is a temperature.

Paragraph 176: The system of Paragraph 172 wherein the controllerdisables the radiofrequency signal generator if the parameter exceeds alimit.

Paragraph 177: The system of Paragraph 172 wherein the controllerconfigures the sequence to minimize the number of configurations, tomaximize the number of ground pads that simultaneously carryradiofrequency current from the ablation electrode, or to maximize thetotal capacity of the ground pads to carry current from the ablationelectrode without burning tissue in contact with any of the ground pads.

Paragraph 178: The system of Paragraph 168 wherein the controllerconfigures the sequence to equalize the RMS current flowing to eachground pad over a time period.

Paragraph 179: The system of Paragraph 168 wherein the sequence includesa nested-simultaneous switching pattern.

Paragraph 180: The system of Paragraph 179 wherein thenested-simultaneous switching pattern is determined and then fixed atthe beginning of the sequence.

Paragraph 181: The system of Paragraph 168 wherein each ground pad isconnected to, and disconnected from, the radiofrequency signal generatorby a switch.

Paragraph 182: A system for tissue ablation that includes aradiofrequency signal generator, a controller, an ablation electrode,and at least two ground pads; wherein the controller can connect eachground pad to the radiofrequency signal generator so that current flowsbetween the ablation electrode and the ground pad through a living body,and the controller can disconnect each ground pad from theradiofrequency signal generator so that current does not substantiallyflow between the ablation electrode and the ground pad; wherein thecontroller disconnects the ground pads from the radiofrequency signalgenerator in an order, each ground pad being disconnected either afteror at the same time as the preceding ground pad in the order; whereinthe controller connects the ground pads to the radiofrequency signalgenerator in the order, each ground pad being connected either before orat the same time as the preceding ground pad in the order; wherein theorder is not predetermined.

Paragraph 183: The system of Paragraph 182 wherein the order or timingby which the controller connects or disconnects ground pads isconfigured to regulate a measured parameter of each ground pad.

Paragraph 184: The system of Paragraph 183 wherein the parameter of eachground pad is the current flowing through each ground pad.

Paragraph 185: The system of Paragraph 183 wherein the parameter of eachground pad is the root-mean-squared current flowing through each groundpad over a time window.

Paragraph 186: The system of Paragraph 183 wherein the parameter of eachground pad is the temperature of each ground pad.

Paragraph 187: The system of Paragraph 183 wherein the order in whichground pads are disconnected is configured to minimize the totalduration for which any of the ground pads is disconnected during thetissue ablation.

Paragraph 188: The system of Paragraph 183 wherein the order in whichground pads are disconnected is configured to maximize the number ofground pads connected at the same time during the tissue ablation.

Paragraph 189: The system of Paragraph 182 wherein when a ground pad isdisconnected, it presently carries the most current among the presentlyconnected ground pads.

Paragraph 190: The system of Paragraph 182 wherein when a ground pad isdisconnected, it presently has the highest temperature among thepresently connected ground pads.

Paragraph 191: The system of Paragraph 182 wherein the order ismonotonically decreasing in the current carried by each pad when allground pads are connected.

Paragraph 192: The system of Paragraph 182 wherein the order ismonotonically decreasing in rate of increase in the temperature of eachground pad when all ground pads are connected.

Paragraph 193: The system of Paragraph 182 wherein the controllerrepeatedly disconnects the ground pads from the radiofrequency signalgenerator in the order, each ground pad being disconnected either afteror at the same time as the preceding ground pad in the order; andrepeatedly connects the ground pads to the radiofrequency signalgenerator in the order, each ground pad being connected either before orat the same time as the preceding ground pad in the order.

Paragraph 194: The system of Paragraph 182 wherein each ground pad isconnected to and disconnected from the radiofrequency signal generatorby means of a switch.

Paragraph 195: A method for distributing radiofrequency current from anablation electrode, through a living body, between at least two groundpads comprising: connecting each of the ground pads to the currentsource so that current flows through each ground pad at the same time;selecting at least one of the ground pads to be disconnected based on atleast one measurement; both disconnecting the selected ground pads fromthe current source, and connecting each of the non-selected ground padsto the current source, so that current does not substantially flowthrough any of the selected ground pads, and current flows through eachof the non-selected ground pads, at the same time.

Paragraph 196: The method of Paragraph 195 performed in whole or in partby an automated controller.

Paragraph 197: The method of Paragraph 195 configured for preventingburning of tissue in contact with a ground pad.

Paragraph 198: The method of Paragraph 195 wherein the at least onemeasurement includes a measurement of the current flowing through aground pad, or a measurement of the temperature of a ground pad.

Paragraph 199: The method of Paragraph 195 configured to regulate atleast one measured parameter of a ground pad.

Paragraph 200: The method of Paragraph 199 wherein the at least onemeasured and regulated parameter includes the current flowing through aselected ground pad, the current flowing through a non-selected groundpad, the temperature of a selected ground pad, or the temperature of anon-selected ground pad.

Paragraph 201: The method of Paragraph 199 wherein regulating a measuredparameter comprises hold the parameter below a limit.

Paragraph 202: The method of Paragraph 199 wherein regulating at leastone measured parameter of a ground pad comprises equalizing the measuredparameter of each of at least two ground pads.

Paragraph 203: The method of Paragraph 195 wherein the at least onemeasurement includes a measurement of the current flowing through eachground pad when current flows through each ground pad at the same time;and said selecting at least one of the ground pads to be disconnectedbased on at least one measurement comprises selecting the one or moreground pads having the highest current measurement, to be disconnected.

Paragraph 204: The method of Paragraph 195 wherein the at least onemeasurement includes a measurement of root-mean-squared current for eachground pad over a time period, and selecting at least one of the groundpads to be disconnected based on at least one measurement comprisesselecting the one or more ground pads having the highest currentmeasurement, to be disconnected.

Paragraph 205: The method of Paragraph 195 wherein the at least onemeasurement includes a measurement of temperature for each ground pad,and selecting at least one of the ground pads to be disconnected basedon at least one measurement comprises selecting the one or more groundpads having the highest temperature measurement, to be disconnected.

Paragraph 206: The method of Paragraph 195 wherein the duration of saidconnecting each of the ground pads to the current source so that currentflows through each ground pad at the same time; or the duration of saidboth disconnecting the selected ground pads from the current source, andconnecting each of the non-selected ground pads to the current source,so that current does not substantially flow through any of the selectedground pads, and current flows through each of the non-selected groundpads, at the same time; is short relative to the thermal response timeof the ground pads.

Paragraph 207: The method of Paragraph 195 and further comprising atleast one repetition of the method of Paragraph 195 during a singleradiofrequency ablation process.

Paragraph 208: The method of Paragraph 207 wherein the same at least oneof the ground pads are selected in each repetition.

Paragraph 209: The method of Paragraph 195 wherein connecting each ofthe ground pads to the current source so that current flows through eachground pad at the same time precedes both disconnecting the selectedground pads from the current source, and connecting each of thenon-selected ground pads to the current source, so that current does notsubstantially flow through any of the selected ground pads, and currentflows through each of the non-selected ground pads, at the same time.

Paragraph 210: The method of Paragraph 195 wherein both disconnectingthe selected ground pads from the current source, and connecting each ofthe non-selected ground pads to the current source, so that current doesnot substantially flow through any of the selected ground pads, andcurrent flows through each of the non-selected ground pads, at the sametime precedes connecting each of the ground pads to the current sourceso that current flows through each ground pad at the same time.

Paragraph 211: The method of Paragraph 195 wherein connecting a groundpad to the current source, and disconnecting the ground pad from thecurrent source, is performed by means of a switch that is connected toboth the ground and the current source.

Paragraph 212: The method of Paragraph 195 and further comprisingapplying the method of Paragraph 195 to the non-selected ground pads.

Paragraph 213: The method of Paragraph 195 and further comprisingrecursively applying the method of Paragraph 195 to the non-selectedground pads of each of at least one recursion of the method of Paragraph195.

Paragraph 214: The method of Paragraph 213 and further comprising one ormore repetitions of the method of Paragraph 213 during a singleradiofrequency ablation process.

Paragraph 215: The method of Paragraph 214 wherein the selected groundpads of each recursion of the method of Paragraph 195 are the same foreach repetition of the Paragraph 214.

Paragraph 216: The method of Paragraph 195 wherein distributingradiofrequency current from an ablation electrode, through a livingbody, between at least two ground pads comprises holding a function ofcurrent for each of the ground pads below a limit.

Paragraph 217: The method of Paragraph 216 wherein the function ofcurrent is the root-mean-squared current over a time window.

Paragraph 218: The method of Paragraph 195 wherein distributingradiofrequency current from an ablation electrode, through a livingbody, between at least two ground pads comprises equalizing a functionof current for each of the ground pads.

Paragraph 219: The method of Paragraph 218 wherein the function ofcurrent is the root-mean-squared current over a time window.

Paragraph 220: The method of Paragraph 195 and further comprisingdisplaying the at least one measurement to a person in real-time.

Paragraph 221: The method of Paragraph 195 and further comprisingdisplaying to person a measurement of a ground pad in real-time.

Paragraph 222: A method for distributing radiofrequency current from anablation electrode among at least two ground pads comprising: selectinga first ground pad based in whole or in part on at least one measurementof a ground pad; and switching among at least two states; wherein thestates include a first state in which the first ground pad and a secondground pad each carry some or all of the current; wherein the statesinclude a second state in which the first ground pad does not carry asubstantial portion of the current, and the second ground pad carriessome or all of the current.

Paragraph 223: The method of Paragraph 222 wherein the at least onemeasurement of a ground pad includes the current flowing through aground pad, the power dissipated in the tissue near the ground pad, orthe temperature of a ground pad.

Paragraph 224: The method of Paragraph 222 wherein said switching amongat least two states comprises repeatedly changing the configuration of aswitching system that connect each ground pad to the source of thecurrent, in order to produce the states.

Paragraph 225: The method of Paragraph 222 performed by an automatedcontroller.

Paragraph 226: The method of Paragraph 222 configured to regulate atleast one measurement of a ground pad.

Paragraph 227: The method of Paragraph 222 configured to regulate atleast one measurement for each ground pad.

Paragraph 228: The method of Paragraph 222 wherein the states can occurin any order, and each state can occur one or more times.

Paragraph 229: The method of Paragraph 222 wherein at one additionalelectrode carries some or all of the current.

Paragraph 230: The method of Paragraph 222 wherein the states include astate in which no ground pad carries a substantial portion of thecurrent.

Paragraph 231: The method of Paragraph 222 wherein there is one or moreground pad that does not carry a substantial portion of the current.

Paragraph 232: The method of Paragraph 222 and further comprisingchanging the selection of the first ground pad at least once during saidswitching among at least two states, based in whole or in part on atleast one measurement of a ground pad.

Paragraph 233: The method Paragraph 222 wherein the states furtherinclude at least one state in which a subset of the ground pads do notcarry a substantial portion of the current, and each of the ground padsthat are not in the subset carries some or all of the current.

Paragraph 234: The method Paragraph 222 wherein at least two of theground pads are combined into a single pad structure within which eachpad is electrically isolated from the other ground pads.

Paragraph 235: The method of Paragraph 222 and further comprisingselecting each of the second through (N−1)-th ground pads based in wholeor in part on at least one measurement of a ground pad; wherein in thefirst state, the second through the (N−1)-th ground pads and an N-ththrough P-th ground pads each carry some or all of the current; whereinfor each integer M in the range two to N, the states include an M-thstate in which each of the first through (M−1)-th ground pads do notcarry a substantial portion of the current, and each of the M-th throughP-th ground pads carries some or all of the current; N being an integernumber greater than two, and P being an integer number that is greaterthan or equal to N.

Paragraph 236: The method of Paragraph 235 and further comprisingchanging the selection any one or more of the first through (N−1)-thground pads at least once, changing the value of N, or changing thevalue of P, during said switching among at least two states, based inwhole or in part on at least one measurement of a ground pad.

Paragraph 237: The method of Paragraph 235 wherein the states include an(N+1)-th state in which none of the first through P-th ground padscarries a substantial portion of the current.

Paragraph 238: A system for tissue ablation that includes aradiofrequency signal generator, a controller, an ablation electrode, atleast two ground pads, and a switching system by means of which eachground pad can be connected to and disconnected from the radiofrequencysignal generator; wherein current from the radiofrequency signalgenerator flows between the electrode and each ground pad through aliving body; wherein the controller turns off the radiofrequency signalgenerator when a ground pad is being connected or disconnected from theradiofrequency signal generator during a tissue ablation process.

Paragraph 239: A system for tissue ablation that includes aradiofrequency signal generator, a controller, an ablation electrode,and at least two ground pads; wherein current from the radiofrequencysignal generator flows between the electrode and each ground pad througha living body; wherein the controller reduces the current when a groundpad is being connected or disconnected from the radiofrequency signalgenerator by a switch in order to prevent undesired stimulation ofexcitable tissue in the living body.

Paragraph 240: A method of avoiding undesired electrical stimulation ofexcitable tissue during a radiofrequency tissue ablation process inwhich a ground pad is connected to or disconnected from the source ofthe radiofrequency signal, comprising reducing or turning off theradiofrequency signal output while a ground pad is in the process ofbeing either connected to or disconnected from the source ofradiofrequency signal.

Paragraph 241: The method of Paragraph 240 wherein the ground pad isconnected to or disconnected from the source by means of a switch.

Paragraph 242: A method of avoiding undesired electrical stimulation ofexcitable tissue during a multi-electrode radiofrequency tissue ablationprocess in which an ablation electrode is connected to or disconnectedfrom the source of the radiofrequency signal, comprising reducing orturning off the radiofrequency signal output while the ablationelectrode is in the process of being either connected to or disconnectedfrom the source of radiofrequency signal.

Paragraph 243: The method of Paragraph 242 wherein the ablationelectrode is connected to or disconnected from the source by means of aswitch.

Paragraph 244: The method Paragraph 242 wherein the multi-electroderadiofrequency tissue ablation process is multi-electrode cooledradiofrequency tissue ablation process.

Paragraph 245: The method Paragraph 242 wherein ablated tissue includesa tumor.

Paragraph 246: The method Paragraph 242 wherein ablated tissue includesa nerve.

Paragraph 247: The method Paragraph 242 wherein ablated tissue is withina large organ, including but not limited to an organ in the list: liver,kidney, lung, pancreas, bone.

Paragraph 248: A system comprising at least one electrode, anerve-stimulation signal generator, and a high-frequency ablation signalgenerator, wherein the system delivers a nerve-stimulation signal to anerve through a first electrode, and the system delivers ahigh-frequency-ablation signal to tissue through a second electrode,such that the nerve is stimulated while tissue is being ablated.

Paragraph 249: The system of Paragraph 248 wherein the high-frequencyablation signal is a signal selected from the group: a radiofrequencyablation signal, a microwave ablation signal, a direct current ablationsignal, a pulsed radiofrequency signal configured to hold thetemperature measured by the second electrode below the neurolytic range,a superposition of a radiofrequency ablation signal and a direct currentablation signal, a superposition of a radiofrequency ablation signal anda direct current ablation signal, a superposition of a radiofrequencyablation signal and a microwave ablation signal.

Paragraph 250: The system of Paragraph 248 or 249 wherein thenerve-stimulation signal is a signal selected from the group: a biphasicsignal, a signal comprising a sequence of biphasic square pulses, asignal comprising a sequence of biphasic square pulses having pulsewidth in the range 0.1-3 milliseconds, a signal comprising a sequence ofbiphasic square pulses having pulse frequency in the range 1 Hz to 200Hz, a signal comprising sinusoidal bursts, a motor nerve stimulationsignal, a nerve-stimulation signal with a frequency in the range 1 Hz to10 Hz, a nerve-stimulation signal with a frequency 2 Hz, anerve-stimulation signal with a frequency in the range 5 Hz, asensory-nerve stimulation signal, a nerve-stimulation signal with afrequency in the range 50 Hz to 200 Hz, a nerve-stimulation signal witha frequency 50 Hz, a peripheral-nerve stimulation signal, acentral-nerve stimulation signal, a high-frequency-block signal, asignal with frequency 2,000 Hz to 50,000 Hz, a nerve stimulation signalconfigured to block transmission of action potentials, a nervestimulation signal with frequency less than 50,000 kHz.

Paragraph 251: The system of Paragraph 248, 249, or 250 wherein thefirst electrode and the second electrode are the same electrode.

Paragraph 252; The system of Paragraph 248, 249, or 250 wherein thefirst electrode and the second electrode are the same active tip on asingle electrode.

Paragraph 253: The system of Paragraph 248, 249, or 250 wherein firstelectrode and the second electrode are physically separate.

Paragraph 254: The system of Paragraph 248, 249, 250, or 251 wherein thetissue being ablated includes a nerve.

Paragraph 255: The system of Paragraph 248, 249, 250, or 251 wherein thetissue being ablated includes the nerve that is stimulated.

Paragraph 256: The system of Paragraph 255 wherein the nerve is aperipheral nerve.

Paragraph 257: The system of Paragraph 248, 249, 250, or 251 wherein thetissue being ablated does not include the nerve that is stimulated.

Paragraph 258: The system of Paragraph 248, 249, 250, 251, 252, 253,254, 255, 256, or 257 wherein the nerve-stimulation signal and thehigh-frequency ablation signal are delivered at the same time.

Paragraph 259: The system of Paragraph 248, 249, 250, 251, 252, 253,254, 255, 256, or 257 wherein the nerve-stimulation signal and thehigh-frequency ablation signal are interleaved in time such that theyare not delivered at the same time.

Paragraph 260: The system of Paragraph 248, 249, 250, 251, 252, 253,254, 255, 256, 257, 258, or 259 and further including a recordingelectrode and monitoring device for measuring electrical signals on thestimulated nerve, while it is being stimulated.

Paragraph 261: A method for reducing or blocking a patient's perceptionof a tissue ablation process comprising applying an electricalstimulation signal to a nerve during the tissue ablation process.

Paragraph 262; The method of Paragraph 261 wherein the tissue ablationprocess comprises a high-frequency electrical tissue ablation process.

Paragraph 263: The method of Paragraph 261 or 262 wherein the tissueablation comprises a radiofrequency ablation process.

Paragraph 264: The method of Paragraph 261 or 262 wherein the tissueablation is selected from the group: high-frequency ablation,radiofrequency ablation, pulsed radiofrequency neuromodulation,microwave ablation, cryogenic ablation, laser ablation, ablation byheating a resistive coil heating, ablation by beating a probe.

Paragraph 265: The method of Paragraph 261 wherein the patient'sperception includes pain.

Paragraph 266: The method of Paragraph 261 wherein the electricalstimulation signal is a high-frequency nerve block signal.

Paragraph 267: The method of Paragraph 261 wherein tissue ablationprocess and the electrical stimulation signal performed by a singlesystem.

Paragraph 268: The method of Paragraph 261 wherein the ablated tissueincludes a nerve.

Paragraph 269: The method of Paragraph 268 wherein the ablated nerve isthe same nerve as the stimulated nerve.

Paragraph 270: The method of Paragraph 261 wherein tissue ablationprocess and the electrical stimulation signal are performed by a singleelectrode.

Paragraph 271: The method of Paragraph 261 and further includingstopping the ablation process, stopping the electrical stimulationsignal, and then testing the result of the ablation process based inwhole or in part of the patient's perception of pain before and afterthe ablation process.

Paragraph 272: A method for monitoring the progress of a nerve ablationprocess comprising: stimulating a nerve during the process of ablatingthe nerve, and monitoring the response of the nerve to the stimulation.

Paragraph 273: The method of Paragraph 272 wherein monitoring comprisesmonitoring the conduction of action potentials through the region of thenerve that is intended to be ablated.

Paragraph 274: The method of Paragraph 272 wherein monitoring comprisingmonitoring the conduction of action potentials through the region of thenerve that is proximate to an ablation probe active tip.

Paragraph 275: The method of Paragraph 272 wherein the location of thenerve ablation process is positioned along the nerve between thelocation nerve stimulation and the location of the monitoring of theresponse of the nerve to the stimulation.

Paragraph 276: The method of Paragraphs 272, 273, 274, or 275 whereinmonitoring is performed by one or more of the methods selected form thegroup: measuring an electrical signal conducted by the nerve, observinga physiological response influenced by the nerve, observing twitchingfrom a muscle innervated by the nerve, monitoring the patient'sperception of the stimulation signal.

Paragraph 277: The method of Paragraph 272, 273, 274, 275, or 276, andfurther comprising: stopping the nerve ablation process when theresponse of the nerve to the stimulation is reduced to below athreshold.

Paragraph 278: The method of Paragraphs 272, 273, 274, 275, 276, or 277wherein the nerve ablation process is of one or more of the typesselected from the group: a radiofrequency ablation, a microwaveablation, a direct current, a pulsed radiofrequency configured to holdthe temperature measured by the second electrode below the neurolyticrange, combined radiofrequency and direct current ablation, cooled RFablation, perfusion RF ablation, combined radiofrequency and microwaveablation.

Paragraph 279: The system of Paragraph 272, 273, 274, 275, 276, 277, or278 wherein the nerve stimulation is of one or more of the typesselected from the group: electrical nerve stimulation, an electricalsignal configured to induce repeated nerve firing, a biphasic signal, asignal comprising a sequence of biphasic square pulses, a signalcomprising a sequence of biphasic square pulses having pulse width inthe range 0.1-3 milliseconds, a signal comprising a sequence of biphasicsquare pulses having pulse frequency in the range 1 Hz to 200 Hz, asignal comprising sinusoidal bursts, a motor nerve stimulation signal, anerve-stimulation signal with a frequency in the range 1 Hz to 10 Hz, anerve-stimulation signal with a frequency 2 Hz, a nerve-stimulationsignal with a frequency in the range 5 Hz, a sensory-nerve stimulationsignal, a nerve-stimulation signal with a frequency in the range 50 Hzto 200 Hz, a nerve-stimulation signal with a frequency 50 Hz, aperipheral-nerve stimulation signal, a central-nerve stimulation signal,mechanical stimulation of the nerve, stimulation of a receptor thatstimulates the nerve, stimulation of a physiologic process thatstimulates the nerve, mechanical manipulation of the patient thatstimulates the nerve.

Paragraph 280: A method wherein an electrical stimulation signal isapplied to a nerve and is configured to block the perception of paingenerated by the ablation of the nerve.

Paragraph 281: The method of Paragraph 280 wherein the electricalstimulation signal induces a high-frequency conduction block.

Paragraph 282: The method of Paragraph 280 wherein the nerve is aperipheral nerve and wherein the electrical stimulation signal isapplied to a location on the nerve that is closer to the spinal cordthan the ablation at which the nerve is being ablated.

Paragraph 283: The method of Paragraph 280 wherein the ablation of thenerve is produced by a high-frequency electrical signal delivered to anelectrode.

Paragraph 284: The method of Paragraph 280 wherein the electricalstimulation signal and the high-frequency electrical signal are producedby the same electrosurgical generator unit.

Paragraph 285: The method of Paragraph 280 wherein the high-frequencyelectrical signal is a radiofrequency signal.

Paragraph 286: A method wherein an electrical stimulation signal isapplied to a nerve at a first location, an ablation process is appliedto the nerve at a second location, and the transmission of nerve signalsgenerated at the first location through the second location aremonitored during the ablation process.

Paragraph 287: The method of Paragraphs 286 wherein the ablation processis a high-frequency ablation process.

Paragraph 288: The method of Paragraph 286 wherein the electricalstimulation signal and the high-frequency ablation process are producedby the same electrosurgical generator unit.

Paragraph 289: The method of Paragraph 286 wherein the ablation processis a radiofrequency ablation process.

Paragraph 290: The method of Paragraph 286 wherein the ablation processis a laser ablation process.

Paragraph 291: The method of Paragraph 286 wherein the transmission ismonitored by placing a recording electrode at a third location along thenerve, wherein the second location is between the first location and thethird location along the nerve.

Paragraph 292: The method of Paragraph 286 wherein the transmission ismonitored by placing a recording electrode within a muscle innervated bythe nerve, and the second location is between the first location and themuscle along the nerve.

Paragraph 293: The method of Paragraph 286 wherein the transmission ismonitored by observation of contractions in a muscle innervated by thenerve, and the second location is between the first location and themuscle along the nerve.

Paragraph 294: A system including a radiofrequency generator and anultrasound imaging machine wherein the radiofrequency generator canmeasure and control the operations of the ultrasound imaging machine,and the ultrasound imaging machine can measure and control theoperations of the radiofrequency generator.

Paragraph 295: A high-frequency electrosurgical generator that canmonitor and control an ultrasound imaging machine.

Paragraph 296: The system of Paragraph 295 wherein the high-frequencygenerator is a radiofrequency generator.

Paragraph 297: The system of Paragraph 295 wherein the high-frequencygenerator is a microwave generator.

Paragraph 298: The system of Paragraph 295 wherein the high-frequencygenerator includes a display on which ultrasound data is displayed.

Paragraph 299: The system of Paragraph 295 wherein the high-frequencygenerator includes a display on which ultrasound settings are displayed.

Paragraph 300: The system of Paragraph 295 wherein the high-frequencygenerator includes user interface elements for control of the settingsand operations of the ultrasound machine.

Paragraph 301: The system of Paragraph 295 wherein the high-frequencygenerator adjusts its signal output in response to data measured fromthe ultrasound imaging machine.

Paragraph 302: The system of Paragraph 295 wherein the high-frequencygenerator automatically adjusts the operation of the ultrasound imaginein response to measurements of an ablation process.

Paragraph 303: The system of Paragraph 295 wherein the ultrasoundmachine and high-frequency generator are in same chassis.

Paragraph 304: The system of Paragraph 295 wherein a single userinterface includes both high-frequency generator and ultrasound machinecontrol functions.

Paragraph 305: The system of Paragraph 295 wherein the control ofultrasound machine is by means of a standardized interface forconnecting a high-frequency electrosurgical generator to an ultrasoundimaging machine.

Paragraph 306: The system of Paragraph 295 wherein the high-frequencygenerator includes a common procedure record including both ultrasoundand radiofrequency data.

Paragraph 307: The system of Paragraph 295 wherein the high-frequencygenerator is of a type selected from the group: radiofrequencygenerator, microwave generator, cooled radiofrequency generator andpump, impedance-controlled cooled radiofrequency tissue ablation, nerveradiofrequency ablation generator, neurological radiofrequency ablationgenerator, radiofrequency ablation generator that includes an integratednerve stimulator.

Paragraph 308: An ultrasound imaging machine that can monitor andcontrol a high-frequency electrosurgical generator.

Paragraph 309: The system of Paragraph 308 wherein the high-frequencygenerator is a radiofrequency generator.

Paragraph 310: The system of Paragraph 308 wherein the high-frequencygenerator is a microwave generator.

Paragraph 311: The system of Paragraph 308 wherein the ultrasoundmachine includes a display on which high-frequency generator data isdisplayed.

Paragraph 312: The system of Paragraph 308 wherein the ultrasoundmachine includes a display on which high-frequency generator settingsare displayed.

Paragraph 313: The system of Paragraph 308 wherein the ultrasoundmachine includes user interface elements for control of thehigh-frequency generator settings and operations.

Paragraph 314: The system of Paragraph 308 wherein the ultrasoundmachine automatically adjusts its data acquisition process in response ameasurement collected by the high-frequency generator.

Paragraph 315: The system of Paragraph 308 wherein the ultrasoundmachine automatically adjusts the operation of the high-frequencygenerator in response to an ultrasound measurement.

Paragraph 316: The system of Paragraph 308 wherein the ultrasoundmachine and high-frequency generator are in same chassis.

Paragraph 317: The system of Paragraph 308 wherein a single userinterface includes control function of both the high-frequency generatorand the ultrasound imaging machine.

Paragraph 318: The system of Paragraph 308 wherein the high-frequencygenerator includes a standardized interface by means of which anultrasound imaging machine can control the high-frequency generator.

Paragraph 319: The system of Paragraph 308 wherein the ultrasoundmachine produces a common procedure record including both ultrasound andradiofrequency data.

Paragraph 320: A system that includes an ultrasound imaging apparatus,an electrosurgical tissue ablation generator, and a user interface whichincludes user controls and a data display for both the ultrasoundimaging apparatus and the electrosurgical tissue ablation generator.

Paragraph 321: The system of Paragraph 320 wherein the user interface isa single user console.

Paragraph 322: A tissue ablation apparatus including an interface towhich an ultrasound imaging machine can connect and thereby control theoperations of the tissue ablation apparatus either automatically or byuser input into the user interface of the ultrasound imaging machine,read data from the tissue ablation apparatus, and display data from thetissue ablation apparatus to the user by means of the user interface ofthe ultrasound imaging machine.

Paragraph 323: The system of Paragraph 322 wherein the ultrasoundimaging machine can be selected from one or more ultrasound imagingmachines configured to connect to the tissue ablation apparatus.

Paragraph 324: The system of Paragraph 322 and further includingpublished specifications for the interface.

Paragraph 325: The system of Paragraph 322 wherein the tissue ablationapparatus is configured to be housed inside the ultrasound imagingmachine's chassis.

Paragraph 326: A ultrasound imaging apparatus including an interface towhich an tissue ablation apparatus can connect and thereby control theoperations of the ultrasound imaging apparatus either automatically orby user input into the tissue ablation machine user interface, read datafrom the ultrasound imaging apparatus, and display data from theultrasound imaging apparatus to the user by means of the user interfaceof the tissue ablation apparatus.

Paragraph 327: The system of Paragraph 326 wherein the tissue ablationapparatus can be selected from one or more tissue ablation apparatusesconfigured to connect to the ultrasound imaging apparatus.

Paragraph 328: The system of Paragraph 326 and further includingpublished specifications for the interface.

Paragraph 329: The system of Paragraph 326 wherein the ultrasoundimaging apparatus is configured to be housed inside the chassis of thetissue ablation apparatus.

Paragraph 330: A method for marketing a tissue ablation apparatuscomprising constructing a tissue ablation apparatus having a dataconnection that provides for monitoring and control of the tissueablation apparatus, and publishing the specification of the dataconnection.

Paragraph 331: A method for marketing a medical imaging apparatuscomprising constructing a medical imaging apparatus having a dataconnection that provides for monitoring and control of the medicalimaging apparatus, and publishing the specification of the dataconnection.

Paragraph 134A. The system of Paragraph 116 and further including aswitching system by means of which each ground pad can be connected toand disconnected from the radiofrequency signal generator, whereinconnecting a ground pad to the radiofrequency signal generator allowsthe flow of current from the radiofrequency signal generator through theground pad, and wherein disconnecting a ground pad from theradiofrequency signal generator substantially stops the flow of currentfrom the radiofrequency signal generator through the ground pad; andfurther including a controller that automatically connects anddisconnects a ground pad from the radiofrequency signal generator toregulate the displayed parameter for the ground pad.

Paragraph 135A. The system of Paragraph 134A wherein the display for aground pad includes a display of a moving average of the current flowingthrough the ground pad over at least one time period during which atleast one ground-pad switch either opens or closes.

Paragraph 136A. The system of Paragraph 134A wherein the display for aground pad includes a display of a root-mean-square moving average ofthe current flowing through the ground pad over at least one time windowduring which at least one ground-pad switch either opens or closes.

Paragraph 137A. The system of Paragraph 134A wherein the controllerturns off the radiofrequency signal generator while a ground pad isbeing connected or disconnected from the radiofrequency signal generatorduring a tissue ablation process.

Paragraph 138A. The system of Paragraph 134A wherein the switchingsystem includes a switch for each ground pad, wherein opening the switchfor a ground pad disconnects the ground pad from the radiofrequencysignal generator, and wherein closing the switch for a ground paddisconnects the ground pad from the radiofrequency signal generator.

Paragraph 139A. The system of Paragraph 134A wherein controller thatautomatically connects and disconnects one or more ground pads from theradiofrequency signal generator to regulate the displayed parameter foreach ground pad.

Paragraph 60A. The system of Paragraph 36 and further includingnumerical display of the duration of each instance of the signal levelbeing in the first range, each instance of the signal level being in thesecond range, or both.

Paragraph 61A. The system of Paragraph 35 and further includingnumerical display of the two or more parameters.

Paragraph 195A. The system of Paragraph 182 and further including anerve-stimulation signal generator that can deliver a nerve-stimulationsignal to the ablation electrode.

Paragraph 196A. The system of Paragraph 183 and further including a userdisplay of the measured parameter of each ground pad.

Paragraph 197A. The system of Paragraph 182 wherein the controller turnsoff the radiofrequency signal generator while a ground pad is in theprocess of being connected to the radiofrequency signal generator or inthe process of being disconnected from the radiofrequency signalgenerator.

A number of embodiments of the invention have been described.Nevertheless, it will be understood that various modifications may bemade without departing from the spirit and scope of the invention.Accordingly, other embodiments are within the scope of the followingclaims. What we claim are the following.

What is claimed is:
 1. A system for tissue ablation including: agenerator of high-frequency signal output; an electrode including anshaft portion adapted to be inserted into the body and adapted to beconnected to the generator, the shaft portion having a tip portion soadapted such that when said shaft portion is inserted into the body, thesignal output is delivered through the tip portion to the bodily tissueto be ablated, said shaft portion having an inner space that can acceptcirculation of coolant to cool said tip portion; a coolant systemadapted to connect to said electrode and supply circulation of coolantto the electrode inner space to cool the electrode tip portion; ameasuring system adapted to measure in real time at least one signaloutput parameter from the list of impedance, current, voltage, andpower; a control system including an automatic controller adapted tocontrol the at least one measured signal output parameter, includingmodulating the signal output to maintain the at least one measuredsignal output parameter at a desired level; a computer graphic displayadapted to plot in real time at least one measured signal outputparameter as a function of a time scale axis.
 2. The system of claim 1wherein the measuring system measures in real time at least two signaloutput parameters from the list of impedance, current, voltage, andpower; and wherein the computer graphic display plots in real time atleast two measured signal output parameters on the same time scale,either next to each other on separate time scale axes, or overlappingeach other on the same time scale axis, to provide a dynamic visualrelationship of the variation of these signal output parameters.
 3. Thesystem of claim 1 wherein the control system switches the level of thesignal output between an ablation range configured to heat tissuesubstantially, and a cooling range configured to allow for cooling ofthe heated tissue, wherein the control system performs the switching inresponse to at least one of the measured signal output parameter inaccordance with the automatic controller.
 4. The system of claim 1wherein the control system alternately switches the level of the signaloutput between an ablation range configured to provide for substantialtissue heating, and a cooling range configured to provide for tissue,and thereby produces a sequence of signal output levels configured tomaintain at least one of the measured signal output parameters in adesired range, in accordance with the automatic controller.
 5. Thesystem of claim 1 wherein the control system produces a sequence of uptimes and down times; wherein during each up time, the signal outputlevel is set to a high level configured to raise tissue temperaturessubstantially; wherein during each down time, the signal output level isset to a low level configured to allow for cooling of tissue cool thatwas heated into the boiling range; and wherein the control system,according to the automatic controller, stabilizes the duration of the uptimes, the duration of down times, and the signal output level duringthe up times to achieve a desired ablation size for a prescribed totalduration of the ablation process.
 6. The system of claim 5 wherein thedurations of the up times and the durations of the down times are eachstabilized to a value in the range 5 to 40 seconds.
 7. The system ofclaim 1 wherein the control system, by means of the automaticcontroller, begins the process of abating tissue by means of theelectrode by automatically ramping up the signal output level until theat least one signal output parameter reaches a prescribed level, andthen the control system continues the process of ablating tissue byautomatically modulating the signal output level according to theautomatic controller to maintain at least one measured signal outputparameter at desired levels to optimize ablation size.
 8. The system ofclaim 1 wherein the tip portion contains a temperature sensor; whereinthe measuring system includes a temperature measuring system adapted toconnect to the temperature sensor and to produce a temperature signalindicative of the temperature in the tip portion; wherein the computergraphic display is adapted to plot the temperature signal in real timeon the same time scale as the time scale of a plotted signal outputparameter.
 9. The system of claim 1 wherein the computer graphic displayplots in real time either power, or current, or both, and at least oneadditional parameter selected from the list voltage, impedance, andtemperature, as a function of the same time scale axis.
 10. The systemof claim 9 wherein the graphic display parameters is color-coded so theparameters can be easily visually differentiated from each other. 11.The system of claim 1 wherein the range of the time scale axis is atleast 720 seconds.
 12. The system of claim 1 wherein if one of thedisplayed signal output parameters is impedance, then the range of theimpedance measurement includes at least the range 40 to 120 ohms. 13.The system of claim 1 wherein if one of the displayed signal outputparameters is current, then the range of said current output measurementincludes at least the range 0 to 2000 mA.
 14. The system of claim 1wherein the generator can produce more than 50 Watts of high-frequencysignal output.
 15. The system of claim 1 wherein the generator canproduce at least 200 Watts of high-frequency signal output.
 16. Thesystem of claim 1 wherein the generator can produce at least 400 Wattsof high-frequency signal output.
 17. The system of claim 1 wherein thegenerator is configured for tumor ablation.
 18. The system of claim 5wherein during each up time, the signal output is on; and wherein duringeach down time, the signal output is off.
 19. A system for ablation oftissue in the body including a generator of radiofrequency or microwavesignal output; an electrode including a shaft portion adapted to beinserted into tissue of a body and adapted to be connected to thegenerator, the shaft portion having a tip portion so adapted that whenthe shaft portion is inserted into the body, the signal output isdelivered through the tip portion to the tissue to be ablated, saidshaft portion having an inner space that can accept circulation ofcoolant to cool said tip portion; a coolant system adapted to connect tosaid electrode and supply circulation of coolant to the inner space tocool said tip portion; a measuring system adapted to measure in realtime the impedance of the signal output and at least one signal outputlevel parameter in the list of power, voltage, and current; a controlsystem including an automatic controller adapted to control theimpedance, wherein the automatic controller modulates at least one ofthe signal output level parameters in the list of power, voltage, andcurrent, wherein the modulation is configured to maintain the impedanceat desired levels; a computer graphic display adapted to plot in realtime the impedance on a first time axis, and the at least one measuredsignal output level parameter on a second time axis, wherein the timeaxes are registered to the same time scale to provide a dynamic visualrelationship of the variation of the impedance and the at least onemeasured signal output level parameter.
 20. The system of claim 19wherein the time axis of the impedance and the time axis of the at leastone measured signal output level parameter are positioned next to eachother.
 21. The system of claim 19 wherein the time axis of the impedanceand the time axis of the at least one measured signal output levelparameter are the same time axis.
 22. The system of claim 19 wherein thecontrol system switches the level of the signal output between anablation range configured to heat tissue substantially, and a coolingrange configured to allow for cooling of the heated tissue, wherein thecontrol system performs the switching in response to the impedance, inaccordance with the automatic controller.
 23. The system of claim 19wherein the modulation of signal output level by the automaticcontroller includes repeated alternations of up times wherein the signaloutput is higher, and down times wherein the signal output is lower, toachieve a stable pattern of impedance, output level modulations, up-timedurations, and down-time durations, until an overall duration of signaloutput has been delivered to produce a desired ablation size; whereinduring each up time, by means of the automatic controller, the controlsystem maintains or increases the output level until the impedance risesabove a threshold value; wherein during each down time, by means of theautomatic controller, the control system produces a low output level fora duration configured to reduce the impedance to a baseline value. 24.The system of claim 23 wherein the output signal is shut off during eachdown time; and wherein the output signal is turned on during each uptime.
 25. The system of claim 19 wherein the tip portion contains atemperature sensor, wherein the measuring system includes a temperaturemeasuring system adapted to connect to the temperature sensor and toproduce a temperature signal indicative of the temperature in the tipportion; wherein the computer graphic display is adapted to plot thetemperature signal in real time on the same time scale as the time scaleof the impedance and the at least one measured signal output levelparameter.
 26. The system of claim 25 wherein the measuring system isadapted to measure the parameters impedance, current, voltage, power,and temperature, and the computer graphic display is adapted to plot allof these parameters in real time, and on the same time scale axis. 27.The system of claim 25 wherein the plots of the measured parameters arecolor coded so they can be easily visually differentiated.
 28. Thesystem of claim 23 wherein after repeated alternations of up time anddown time, the duration of the up times and the duration of the downtimes both stabilize to values in the range 5 to 40 seconds.
 29. Thesystem of claim 19 wherein each time axis has a range of at least 720seconds.
 30. The system of claim 19 wherein the range of impedancemeasurement includes at least the range 40 to 120 ohms.
 31. The systemof claim 19 wherein if current is one of the measured signal outputlevel, then current-measurement range includes at least the range 0 to2000 mA.
 32. The system of claim 19 wherein the electrode shaft portionincludes a metal tube that is insulated over its surface except for thetip portion which is uninsulated so that when said shaft portion isinserted into the tissue of the body, and said generator is connectedelectrically to the metal tube of the shaft portion, then the signaloutput current flows into the tissue only from of the tip portion toproduce heating of the tissue.
 33. The system of claim 19 wherein asurface portion of the electrode tip portion is made echogenic by asurface treatment that reflects ultrasound signals preferentially sothat when an ultrasound imaging machine is used to image bodily tissuein which the electrode tip portion is inserted, the echogenic surfaceportion is prominently visible to indicate the position of the tipportion in the tissue.
 34. The system of claim 33 wherein the echogenicsurface portion includes a multiplicity of surface indentations in thesurface of the tip portion.
 35. A system for tissue ablation thatincludes a radiofrequency generator and a graphic display, wherein theradiofrequency generator is configured to apply a radiofrequency signalto an ablation electrode that is in contact with bodily tissue; whereinthe graphic display is configured plot in real time and on one timeaxis, two or more parameters of the signal delivered to the ablationelectrode; wherein each parameter is selected from the list: impedance;voltage; current; power; a measurement of the signal; mathematicalfunctions taking one or more of the arguments impedance, voltage,current, power, and a measurement of the signal.
 36. The system of claim35 and further including a controller configured to automaticallyalternate the signal level between a first range configured to heattissue, and a second range configured to allow for cooling of heatedtissue.
 37. The system of claim 36 wherein the controller switches thesignal level from the first range to the second range based in whole orin part on an indication of boiling or impending boiling in tissueheated by the ablation electrode, and wherein the controller switchesthe signal level from the second range to the first range after aduration configured to allow for dissipation of gas bubbles formed inthe tissue due to boiling.
 38. The system of claim 36 wherein thecontroller changes the signal level from the first range to the secondrange based in whole or in part on an increase in a measured impedance.39. The system of claim 38 wherein one of the plotted parameters isimpedance, one of the plotted parameters is current, and the first rangeis a range of radiofrequency current levels.
 40. The system of claim 36wherein the controller changes the signal level from the first range tothe second range based in whole or in part on a change in one or moremeasured parameters in the list voltage, current, power.
 41. The systemof claim 36 wherein the controller changes the signal level from thesecond range to the first range based on in whole or in part a measuredimpedance.
 42. The system of claim 36 wherein the ablation electrode isinternally-cooled and the controller is configured to optimize aparameter of tissue heating by the ablation electrode.
 43. The system ofclaim 36 wherein the ablation electrode is internally-cooled and thecontroller is configured to maximize the volume of tissue heated by theinternally-cooled ablation electrode.
 44. The system of claim 36 whereinthe first range is a range of signal levels of one type, wherein thetype is selected from the list current, power, voltage.
 45. The systemof claim 36 wherein the first range is a range radiofrequency currentvalues.
 46. The system of claim 35 wherein the ablation electrode isinternally-cooled.
 47. The system of claim 35 wherein the ablationelectrode is not internally-cooled.
 48. The system of claim 35 whereinthe ablation electrode includes a temperature sensor.
 49. The system ofclaim 35 wherein the ablation electrode does not include a temperaturesensor.
 50. The system of claim 35 wherein one of the plotted parametersis impedance.
 51. The system of claim 35 wherein one of the plottedparameters is current.
 52. The system of claim 35 wherein one of theplotted parameters is impedance, and one of the plotted parameters iscurrent.
 53. The system of claim 35 wherein the graphic display isfurther configured to plot a temperature of the ablation electrode inreal time on the time axis.
 54. The system of claim 35 wherein one ofthe plotted parameters is impedance, one of the plotted parameters iscurrent, and the graphic display is further configured to plot atemperature of the ablation electrode in real time on the time axis. 55.The system of claim 35 wherein the graphic display is further configuredto plot a temperature measured at a distance from the ablationelectrode.
 56. The system of claim 35 and further including a controllerthat can automatically regulate the signal level delivered to theablation electrode, wherein the signal level is a parameter of thesignal selected from the list: impedance; voltage; current; power; ameasurement of the signal; a mathematical function taking one or more ofthe arguments impedance, voltage, current, power, and a measurement ofthe signal.
 57. The system of claim 35 wherein the radiofrequencygenerator delivers one or more radiofrequency signals to one or moreablation electrodes, and for each ablation electrode, the graphicdisplay plots in real time and on a time axis, two or more parameters ofthe signal delivered to the ablation electrode; wherein each parameteris selected from the list: impedance; voltage; current; power; ameasurement of the signal delivered to the ablation electrode;mathematical functions taking one or more of the arguments impedance,voltage, current, power, and a measurement of the signal delivered tothe ablation electrode.
 58. The system of claim 57 wherein the graphicdisplay positions all the plots of more than one electrode on the sametime axis.
 59. The system of claim 57 wherein the graphic displayincludes a different time axis for the plots of each of the one or moreablation electrodes.
 60. The system of claim 36 and further includingnumerical display of the duration of each instance of the signal levelbeing in the first range, each instance of the signal level being in thesecond range, or both.
 61. The system of claim 35 and further includingnumerical display of the two or more parameters.
 62. A system for tissueablation that includes a radiofrequency generator, a controller, and agraphic display, wherein the radiofrequency generator delivers aradiofrequency signal output to an electrode inserted into bodilytissue; wherein the controller automatically alternates between a firststate and a second state; wherein in the first state, the controllermaintains the signal output at a higher level configured to raise thetemperature of a substantial portion of the bodily tissue to adestructive temperature; wherein in the second state, the controllermaintains the signal output at a lower level configured to allow thetemperature of heated bodily tissue to cool substantially; wherein thegraphic display plots one or more parameters of the signal output as afunction of time; wherein each parameter can be selected from the list:impedance, current, power, voltage, duty cycle, temperature, time, asignal output level, a measurement of the signal output, a parameter ofthe signal output, a time average of a parameter of the signal output,the RMS value of a parameter of the signal output over a time window, amathematical function of one or more parameters of the signal output.63. The system of claim 60 and further including a coolant supply,wherein the electrode is cooled by the coolant supply.
 64. The system ofclaim 60 wherein the controller switches from the first state to thesecond state when a measurement indicates the presence ofhigh-temperature vapor in tissue near the electrode.
 65. The system ofclaim 60 wherein the controller switches from the first state to thesecond state in response to a change in a measured impedance.
 66. Thesystem of claim 60 wherein the duration for which the controller remainsin the second state before switching to the first state is configured toprovide for dissipation of high-temperature vapor in tissue near theelectrode active tip.
 67. The system of claim 60 wherein the controllerprevents switching from the second state to the first state unless anelevated impedance decreases to a lower value.
 68. The system of claim60 wherein the higher level is an RF current level or a range of RFcurrent levels.
 69. The system of claim 60 wherein the higher level isan RF power level or a range of RF power levels.
 70. The system of claim60 wherein the higher level is an RF voltage level or a range of RFvoltage levels.
 71. The system of claim 60 wherein the duration of aninstance of the first state or of an instance of the second state isgreater than 5 seconds.